Multiplexed diagnostic detection apparatus and methods

ABSTRACT

Disclosed herein are devices configured for the amplification and detection of multiple targets from a sample, and methods of using the same. The devices disclosed herein comprise microfluidic cartridges have a first stage (amplification) and a second (detection) stage. The two-stage design of the cartridges enables testing for multiple targets within a sample, i.e., from a single nucleic acid amplification reaction. Methods for the amplification and detection of a plurality of target nucleic acids from a sample are also disclosed herein.

CLAIM OF PRIORITY

The present application is a continuation of U.S. application Ser. No. 14/267,232, filed on May 1, 2014 and scheduled to issue as U.S. Pat. No. 11,453,906 on Sep. 27, 2022, which is a continuation of International Application No. PCT/US2012/063091, filed on Nov. 1, 2012, which claims priority to U.S. Provisional Application Ser. No. 61/556,032, filed Nov. 4, 2011. Each of the above applications is hereby incorporated by reference in its entirety.

STATEMENT REGARDING FEDERALLY SPONSORED R&D

The research leading to the present invention was supported, at least in part, by a grant from the National Institutes of Health. Accordingly, the Government may have certain rights in the invention.

TECHNICAL FIELD

The apparatus and methods disclosed herein relate generally to the high-throughput, automated execution of nucleic acid based assays, such as Polymerase Chain Reaction (PCR) in a microfluidic cartridge.

BACKGROUND

The medical diagnostics industry is a critical element of today's healthcare infrastructure. At present, however, in vitro diagnostic analyses, no matter how routine, have become a bottleneck in patient care. There are several reasons for this. First, many diagnostic analyses can only be done with highly specialized equipment that is both expensive and only operable by trained clinicians. Such equipment may be found in only a few locations—often just one in any given urban area. This requires hospitals to send out samples for analyses to these locations, thereby incurring shipping costs and transportation delays, and possibly even sample loss or mishandling. Second, the equipment in question is typically not available “on-demand” but instead runs in batches, thereby delaying the processing time for many samples as they must wait for a machine to reach capacity before they can be run.

Understanding that diagnostic assays on biological samples may break down into several key steps, it is often desirable to automate one or more steps. For example, a biological sample, such as those obtained from a patient, can be used in nucleic acid amplification assays, in order to amplify a target nucleic acid (e.g., DNA, RNA, or the like) of interest. Once amplified, the presence of a target nucleic acid, or amplification product of a target nucleic acid (e.g., a target amplicon) reactor can be detected, wherein the presence of a target nucleic acid and/or target amplicon is used to identify and/or quantify the presence of a target (e.g., a target microorganism or the like). Often, nucleic acid amplification assays involve multiple steps, which can include nucleic acid extraction, nucleic acid amplification, and detection. It is desirable to automate certain steps of these processes.

There is a need for improved methods and devices for carrying out diagnostic assays on multiple biological samples in parallel. The embodiments described herein address this need and can advantageously be used in high throughput and multiplexed amplification and detection.

SUMMARY OF THE INVENTION

Certain embodiments disclosed herein contemplate a microfluidic cartridge having a plurality of sample lanes, each lane comprising a microfluidic network having, in fluid communication with one another, an inlet, an amplification chamber, a first amplification valve upstream of the amplification chamber and a second amplification valve downstream of the amplification chamber, a first amplification gate upstream of the amplification chamber and a second amplification gate downstream of the amplification chamber, a first channel leading from the inlet, via the first amplification valve and first amplification gate, to the amplification chamber, a plurality of detection chambers, a first detection valve upstream of the plurality of detection chambers and a second detection valve downstream of the plurality of detection chambers, and a second channel leading from the amplification chamber, via the second amplification gate and first detection valve, to the plurality of detection chambers.

Certain embodiments can further include a third channel in each of the microfluidic networks, the third channel leading from the amplification chamber, via the second amplification valve, to a first vent. Certain embodiments can further include a fourth channel in each of the microfluidic networks, the fourth channel leading from the plurality of detection chambers, via the second detection valve to a second vent.

Each of the plurality of sample lanes can be configured to amplify one or more polynucleotides independently of the other lanes and the amplification can be conducted by real-time amplification in the amplification chambers. Each of the inlets can be configured to accept a quantity of sample from a pipette tip and the quantity of each sample can be from 0.01-50 μl, e.g., 1-20 μl, such as 0.1 μl, 0.2 μl, 0.3 μl, 0.4 μl, 0.5 μl, 0.6 μl, 0.7 μl, 0.8 μl, 0.9 μl, 1 μl, 2 μl, 3 μl, 4 μl, 5 μl, 6 μl, 7 μl, 8 μl, 9 μl, 10 μl, 11 μl, 12 μl, 13 μl, 14 μl, 15 μl, 16 μl, 17 μl, 18 μl, 19 μl, 20 μl, or more, or any amount in between. The inlets of the respective plurality of sample lanes can be spaced apart from one another to permit simultaneous loading from a multiple-pipette head dispenser. The amplification valves can include a temperature responsive substance that melts upon heating to seal a channel that communicates with the amplification chamber. The detection valves can comprise a temperature responsive substance that melts upon heating in order to seal a channel that communicates with the plurality of detection chambers. The amplification gates can include a temperature responsive substance that melts upon heating to open a channel that communicates with the amplification chamber. The detection gates can comprise a temperature responsive substance that melts upon heating in order to open a channel that communicates with the plurality of detection chambers. The amplification chamber can have a volume of 1-25, e.g., 5-10 μl. The plurality of detection chambers can each have a volume less than the volume of the corresponding amplification chamber, e.g., approximately 1 μl-5 μl. In some embodiments, the microfluidic cartridge of can have 12 sample lanes. In some embodiments, the microfluidic cartridge can include one or more detection windows disposed over the detection chambers.

Certain embodiments disclosed herein contemplate a diagnostic apparatus comprised of the microfluidic cartridge, and which further includes a plurality of separately controllable amplification heat sources thermally coupled to the amplification chambers. The apparatus can further include a plurality of detection heat sources thermally coupled to the detection chambers, wherein each amplification valve and each detection valve comprises a separately controllable valve heat source thermally coupled thereto, and each amplification gate comprises a separately controllable gate heat source thermally coupled thereto.

The apparatus can further include a multiple-pipette head dispenser, wherein the dispenser can be configured to introduce a plurality of samples into the plurality of sample lanes simultaneously. The dispenser can be configured to apply physical pressure to the microfluidic cartridge in order to bring the cartridge and the heaters in thermal communication with each other. The dispenser can be configured to introduce fluidic pressure into the plurality of sample lanes in order to move the plurality of samples.

In some embodiments, the detection heat source for each detection chamber can be individually and separately controllable. In other embodiments, the detection heat sources can also be separately controllable in pairs, in threes, fours, fives, sixes, sevens, eights, nines, tens, elevens, twelves, etc., wherein. In some embodiments, the detection heat sources themselves can also be separately controllable as a group of heat sources associated with the detection chambers of one (or more) sample lane(s).

The apparatus can further include an detector head having plurality of detector pairs, wherein each detector pair is comprised of an LED and a photodiode and each detector pair can be configured to detect the presence of one or more analyte(s), e.g., target nucleic acids of an amplified sample in the detection chambers. Two detector pairs of the detector head can be aligned collinearly and configured to detect the presence of one or more analyte(s) in two detection chambers of the plurality (e.g., six) detection chambers associated with one sample lane.

Certain embodiments of the disclosure include a method of amplifying a target nucleic acid in a sample including providing a microfluidic network, introducing the sample into the microfluidic network, the network comprising an amplification chamber and a plurality of detection chambers downstream of the amplification chamber, isolating the sample in the amplification chamber by closing amplification valves in the microfluidic network upstream and downstream of the amplification chamber, thermal cycling the amplification chamber under amplification conditions to create an amplified sample, wherein the amplified sample comprises a target amplicon when the sample comprises the target nucleic acid, opening an amplification gate upstream of the amplification chamber; and moving the amplified sample downstream to the plurality of detection chambers.

In certain embodiments, isolating the sample in the amplification chamber by closing amplification valves can include heating a temperature responsive substance to seal one or more channels that communicate with the amplification chamber and opening an amplification gate upstream of the amplification chamber can include heating a temperature responsive substance to remove the substance from an upstream channel in communication with the amplification chamber. Moving the amplified sample downstream can include applying fluidic pressure to the network and applying fluidic pressure to the network can include discharging fluid from a pipette tip into an inlet of the microfluidic network. The fluid discharged from the pipette tip may be a gas.

The method of amplifying a target nucleic acid can also include isolating the sample in the plurality of detection chambers by closing detection valves upstream and downstream of the plurality of detection chambers and contacting the amplified sample in one of more of the plurality of detection chambers with a detection probe, wherein the detection probe is specific for the target amplicon. The method can also include detecting the presence of the target amplicon in the sample in at least one of the detection chambers, which can be performed by contacting the amplified sample with a detection probe, wherein the detection probe is specific for the target amplicon. The detection probe can include a fluorescent moiety, and detecting the presence of the target amplicon in the amplified sample can include emitting light from a light source to activate the detection probe, and measuring the fluorescence of the detection probe with a photodiode.

In certain embodiments of the disclosure, the method can also include applying physical pressure to the microfluidic network in order to place the network and one or more heat sources in thermal communication. Applying physical pressure can include applying a force from a pipette head dispenser on the microfluidic network. The method of amplifying a target nucleic acid in a sample can be performed simultaneously on a plurality of networks, the plurality of networks comprising a microfluidic cartridge.

The method can further include amplifying a second target nucleic acid in the sample, wherein the amplified sample can include a second target amplicon when the sample comprises the second target nucleic acid. The method can further include detecting the presence of the target amplicon, the second target amplicon, or both in at least one of the detection chambers. Detecting the presence of the second target amplicon can include contacting the amplified sample with a second detection probe, wherein the second detection probe is specific for the second target amplicon. The second detection probe can be a second fluorescent moiety, and detecting the presence of the second target amplicon in the amplified sample can include emitting light from a light source to activate the second detection probe, and measuring the fluorescence of the second detection probe with a photodiode. The first fluorescent moiety and the second fluorescent moiety can be the same or the first fluorescent moiety and the second fluorescent moiety can be different. The detection probe and the second detection probe can be a capture nucleic acid and second capture nucleic acid, respectively, and the T_(m) of the detection probe and the second detection probe can be different. The detection probe can further include a quencher moiety. The second detection probe can include a second quencher moiety.

The thermal cycling can be an assay selected from the group consisting of: polymerase chain reaction, ligase chain reaction, nucleic acid sequence-based amplification, self-sustained sequence replication, strand displacement amplification, and branched DNA signal amplification. The thermal cycling can be a multiplex polymerase chain reaction. The thermal cycling of each of the plurality of networks can be independently controlled.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is a front plan view of a diagnostic apparatus as used in certain of the embodiments.

FIG. 1B is a top perspective view of the diagnostic apparatus of FIG. 1A showing certain internal components of the apparatus.

FIG. 1C illustrates an interior view of the diagnostic apparatus of FIGS. 1A and 1B.

FIG. 2 is a top plan view of a microfluidic cartridge used in certain of the embodiments.

FIG. 3 shows a single sample lane used in certain of the embodiments, the sample lane being part of the microfluidic network of the microfluidic cartridge of FIG. 2 .

FIG. 4A is a representation of a valve used in certain of the embodiments of the microfluidic network of FIG. 3 .

FIG. 4B shows the valve of FIG. 4A in an open state.

FIG. 4C shows the valve of FIG. 4A in a closed state.

FIG. 5 is a representation of a gate used in certain embodiments of the microfluidic network of FIG. 3 .

FIG. 6 shows an interior view of the diagnostic apparatus with the fluid dispenser positioned over the cartridge.

FIG. 7A illustrates an exterior view of the heater/optical module.

FIG. 7B illustrates an isometric view of the optical unit of the heater/optical module of FIG. 7A, the optical unit having the side cover removed.

FIG. 7C illustrates a bottom view of the optical module of FIG. 7A.

FIG. 8 illustrates a cross-sectional view of the detector head used within the optical unit, the cross-sectional view taken along line 8 of FIG. 7B.

FIG. 9 illustrates a top plan view of a heater substrate.

FIGS. 10A-10D illustrate the movement of fluid in the sample lane of a microfluidic cartridge.

FIGS. 11A-11D illustrate the movement of the detector head across the microfluidic cartridge.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

Before the embodiments are further described, it is to be understood that this invention is not limited to particular embodiments described, as such may, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting.

Where a range of values is provided, it is understood that each intervening value, to the tenth of the unit of the lower limit unless the context clearly dictates otherwise, between the upper and lower limit of that range and any other stated or intervening value in that stated range is encompassed within the embodiments. The upper and lower limits of these smaller ranges may independently be included in the smaller ranges and are also encompassed within the embodiments, subject to any specifically excluded limit in the stated range. Where the stated range includes one or both of the limits, ranges excluding either both of those included limits are also included in the embodiments.

Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which the embodiments belong. Although any methods and materials similar or equivalent to those described herein may also be used in the practice or testing of the embodiments, the preferred methods and materials are now described. All publications mentioned herein are incorporated herein by reference to disclose and describe the methods and/or materials in connection with which the publications are cited.

It must be noted that as used herein and in the appended claims, the singular forms “a,” “and,” and “the” include plural referents unless the context clearly dictates otherwise. Thus, for example, reference to “a method” includes a plurality of such methods and equivalents thereof known to those skilled in the art, and so forth.

The publications discussed herein are provided solely for their disclosure prior to the filing date of the present application. Nothing herein is to be construed as an admission that the present invention is not entitled to antedate such publication by virtue of prior invention. Further, the dates of publication provided may be different from the actual publication dates which may need to be independently confirmed.

Definitions

In the description that follows, a number of terms are used extensively. The following definitions are provided to facilitate understanding of the invention.

As used herein, the term “microfluidic” refers to volumes of less than 1 ml, preferably less than 0.9 ml, e.g., 0.8 ml, 0.7 ml, 0.6 ml, 0.5 ml, 0.4 ml, 0.3 ml, 0.2 ml, 0.1 ml, 90 μl, 80 μl, 70 μl, 60 μl, 50 μl, 40 μl, 30 μl, 20 μl, 10 μl, 5 μl, 4 μl, 3 μl, 2 μl, 1 μl, 0.9 μl, 0.8 μl, 0.7 μl, 0.6 μl, 0.5 μl, 0.4 μl, 0.3 μl, 0.2 μl, 0.1 μl, or less, e.g., nanoliter volumes in the range of 10-500 nanoliters, such as 100 nanoliters.

As used herein, the term “cartridge” refers to a unit that may be disposable, or reusable in whole or in part, and that is configured to be used in conjunction with some other apparatus that has been suitably and complementarily configured to receive and operate on (such as deliver energy to) the cartridge.

As used herein, the term “TRS”, “thermo-responsive substance” or “temperature responsive substance” refers to a substance that changes physical character upon heating, and that is relatively immobile at a first temperature and more mobile at a second temperature. A mass of TRS can be an essentially solid mass or an agglomeration of smaller particles. Examples of TRS's include, but are not limited to a eutectic alloy (e.g., a solder), wax (e.g., an olefin), polymers, plastics, and combinations thereof. A TRS can also be a blend of variety of materials, such as an emulsion of thermoelastic polymer blended with air microbubbles (to enable higher thermal expansion, as well as reversible expansion and contraction), polymer blended with expancel material (offering higher thermal expansion), polymer blended with heat conducting microspheres (offering faster heat conduction and hence, faster melting profiles), or a polymer blended with magnetic microspheres (to permit magnetic actuation of the melted thermoresponsive material).

As used herein, the term “target nucleic acid” refers to a nucleic acid of interest. The term nucleic acid can refer to polynucleotides, such as deoxyribonucleic acid (DNA) or ribonucleic acid (RNA), oligonucleotides, fragments generated by the polymerase chain reaction (PCR), and fragments generated by any of ligation, scission, endonuclease action, and exonuclease action. Nucleic acid molecules can be composed of monomers that are naturally-occurring nucleotides (such as DNA and RNA), or analogs of naturally-occurring nucleotides (e.g., α-enantiomeric forms of naturally-occurring nucleotides), or a combination of both. Modified nucleotides can have alterations in sugar moieties and/or in pyrimidine or purine base moieties. Nucleic acid monomers can be linked by phosphodiester bonds or analogs of such linkages. Analogs of phosphodiester linkages include phosphorothioate, phosphorodithioate, phosphoroselenoate, phosphorodiselenoate, phosphoroanilothioate, phosphoranilidate, phosphoramidate, and the like. The term “nucleic acid molecule” also includes so-called “peptide nucleic acids,” which comprise naturally-occurring or modified nucleic acid bases attached to a polyamide backbone. Nucleic acids can be either single stranded or double stranded.

“Nucleic acid amplification assay” refers to any procedure that amplifies target nucleic acids from a template, including but not limited to polymerase chain reaction, e.g., multiplex PCR, ligase chain reaction (LCR), transcription-based amplification systems (TAS), self-sustained sequence replication (3SR), nucleic acid sequence-based amplification (NASBA), strand displacement amplification (SDA) and branched DNA (bDNA) (Persing et al. (1993) Diagnostic Molecular Microbiology: Principles and Applications (American Society for Microbiology, Washington, D.C.).

T_(m), or “melting temperature” refers to the temperature at which half of a given number of nucleic acid duplexes have separated into single strands—a phenomenon also referred to as “denaturing” or “de-annealing.” The melting temperature of a probe or primer—more precisely, the duplex formed by the probe or primer and a complementary single oligonucleotide strand—represents the single most widely used parameter to guide the design of probes and primers in assays involving hybridization. Many commercial software packages are available for this purpose, e.g., OLIGO™, VISUALOMP™, PRIMERSELECT™, ARRAY DESIGNER™, PRIMER3™, and others.

Diagnostic Apparatuses

Provided herein are diagnostic devices, or diagnostic apparatuses, that are configured to test whether an analyte of interest, e.g., a target nucleic acid, is present in a sample. More specifically, the diagnostic devices disclosed herein are configured for the amplification and/or detection of target nucleic acids in a sample, within a microfluidic cartridge.

In accordance with the embodiments disclosed herein, provided is a diagnostic device or diagnostic apparatus that comprises one or more of the following components: a microfluidic cartridge, a plurality of heat sources, a pipette-head dispenser, and an optical module. The components may be integral to the diagnostic device. Alternatively, the components may be removably incorporated into the device. For example, the microfluidic cartridge of the device can represent a removable/disposable component of the device as a whole, whereas the heat sources can be integral to the device.

The diagnostic devices disclosed herein are preferably configured to perform a plurality of nucleic acid amplification reactions in a plurality of microfluidic amplification chambers within a microfluidic cartridge, as well as to detect a plurality of target nucleic acids within a plurality of detection chambers within the microfluidic cartridge.

In some embodiments, the devices are configured to enable thermal cycling (e.g., cycles of heating and cooling) of amplification chambers and/or detection chambers within a microfluidic cartridge. Thermal cycling of the reaction chambers and detection chambers can be used to enable amplification of nucleic acids, e.g., target nucleic acids, as well as detection of nucleic acids, e.g., by observing the melting curves of amplified sample.

A PCR protocol may comprise guidelines for performing the successive annealing and denaturing of the polynucleotides in the reaction chamber prior to detection. Such guidelines, comprising a time profile for heating the chamber, may be referred to as a “protocol.” In certain embodiments, the apparatus may comprise an aperture plate which facilitates consistent heating and cooling of various reaction chambers, e.g., amplification chambers and/or detection chambers within a microfluidic cartridge by applying pressure to the cartridge.

Turning to the figures, FIGS. 1A and 1B show a diagnostic apparatus 10 of certain of the present embodiments. In the embodiment illustrated in FIG. 1A, the diagnostic apparatus includes an apparatus housing 30. The housing 30 may ensure a controlled environment for processing of the microfluidic samples and for preventing undesirable light from entering the detection space. The housing 30 may comprise a cover 16 which includes a handle 14 and a translucent window 12. The cover 16 may be brought down to close the opening in the front of the diagnostic apparatus 10 when the diagnostic apparatus 10 is in operation.

As seen in the embodiments shown in FIGS. 1A and 1B, the diagnostic apparatus 10 may house two specimen racks 24 a, 24 b in a front portion of the diagnostic apparatus 10. The skilled artisan will appreciate, however, that the depiction of the diagnostic apparatus in FIGS. 1A and 1B is exemplary only, and that in some embodiments, the apparatus can be configured to house more than two specimen racks, e.g., three, four, five, six, seven, eight, nine, ten, or more specimen racks. Preferably, the apparatus is configured to house the same number of specimen racks, e.g., two, as microfluidic cartridges.

In some embodiments, each specimen rack 24 a, 24 b can include multiple holders 26. The holders 26 can include receptacles for holding diagnostic reagents, such as nucleic acid amplification reagents. The racks 24 may also include specimen tubes (not shown) and mixing tubes (not shown) for preparing diagnostic-ready samples, such as amplification-ready samples. The apparatus 10 may prepare the desired reagents in the racks 24 a, 24 b using the dispenser 400. Further description of various fluid dispensers may be found in e.g., U.S. Patent Application Publication 2009-0130719 and U.S. Patent Application Publication 2009-0155123, incorporated herein by reference in their entirety. The prepared fluids may then be transferred to a microfluidic cartridge and be inserted into heater/optical modules 500 a, 500 b for processing and analysis.

In some embodiments, the reaction chambers within the microfluidic cartridge(s) (discussed below) can include one or more reagents, buffers, etc., used in the assays described herein, e.g., amplification and/or detection. For example, in some embodiments, the reaction chambers of the microfluidic cartridge can include, e.g., amplification primers, probes, nucleotides, enzymes such as polymerase, or the like. By way of example, in some embodiments, the reaction chambers can include lyophilized reagents, to which processed biological sample (e.g., a solution of extracted nucleic acids) can be added.

FIG. 1A is a front plan view of the diagnostic apparatus 10 of certain of the embodiments. As shown in FIG. 1A, the diagnostic apparatus 10 can include a fluid dispenser 400, mounted on a lateral rail 20. The lateral rail 20 may be part of a motor-driven gantry 18, which may also include a fore-aft rail 22 (not shown). The fore-aft rail 22 may be connected to the lateral rail 20 and mounted perpendicularly to the lateral rail 20 in the diagnostic apparatus 10.

FIG. 1A further illustrates a cover 28 over the heater/optical modules 500 a, 500 b. Receiving trays 520 a and 520 b may be located beneath or within the housing of the heater/optical modules 500 a, 500 b. Receiving tray 520 a is illustrated in an open position, making it available to receive a microfluidic cartridge 200. Receiving tray 520 b is illustrated in a closed position. Closing the tray not only places the reagents in the appropriate position for processing, but also further protects the interior of the heater/optical modules from receiving unwanted or stray light. Introduction of stray or unwanted light into the detection area may cause erroneous fluorescent levels, e.g., that include fluorescence derived from light which is not emitted from the reaction chamber.

FIG. 1B is a perspective view of the diagnostic apparatus 10 showing certain of the internal components found in certain of the embodiments. To better illustrate certain features, the apparatus housing 30, the cover 16, and the heater/optical cover 28 found in FIG. 1A are not shown in FIG. 1B. Shown in FIG. 1B is the gantry 18, including the lateral rail 20 and fore-aft rail 22. The fluid dispenser 400 can be mounted on the lateral rail 20 and can slide laterally along the long lateral rail 20. The lateral rail 20 can be connected to the fore-aft rail 22 which itself may move in the fore-aft direction. In this manner the fluid dispenser 400 is available to move in the plane of the x and y axes throughout the diagnostic device 10. As described below, in some embodiments, the fluid dispenser 400 can also to move up and down in the z-plane on the lateral rail 20, thereby giving the dispenser 400 the ability to move in three directional degrees throughout the diagnostic device 10.

Also shown in FIG. 1B are heater/optical modules 500 a, 500 b. In FIG. 2B, the heater/optical modules are shown without cover 28. The receiving trays 520 a and 520 b are depicted in the open position and are each holding microfluidic cartridges 200. In some embodiments, the receiving trays can each include a heater substrate 600 (not shown) residing beneath and in thermal communication with, each of the microfluidic cartridges 200. The heater/optical modules 500 a, 500 b may also each include a detector head 700 (not shown) described in greater detail below.

As will be described in more detail below, the diagnostic apparatus 10 may be configured to conduct real-time analysis on one or more samples. The sample to be tested may first be placed in a specimen tube (not shown) on the rack 24 a or 24 b. Reagents such as amplification reagents, (e.g., amplification primers, buffers, nucleotides, and the like) and/or detection reagents (e.g., probes and the like) may be located in the holders 26 on the rack 24 a inside the diagnostic apparatus 10. The fluid dispenser 400 may mix and prepare the sample for diagnostic testing and may then deliver the prepared sample to the microfluidic cartridge 200 for thermal cycling and target nucleic acid detection in the heater/optical modules 500 a, 500 b. Alternatively, the fluid dispenser 400 may deliver nucleic acid samples to the reaction chambers of the microfluidic cartridge, wherein the reaction chambers, e.g., amplification chambers or detection, of the microfluidic cartridge already contain reagents for an amplification reaction or detection. Certain details and methods for processing polynucleotides may be found in e.g., U.S. Patent Application Publication 2009-0131650, U.S. Patent Application Publication 2010-0009351, U.S. Patent Application Publication 2009-0134069, all of which are incorporated herein by reference in their entirety.

FIG. 1C illustrates an interior view of the diagnostic apparatus 10, showing the rack 24 a holding a number of sample tubes 32 and reagent holders 26. FIG. 1C also shows a cartridge 200 situated in the receiving tray 520 a. The receiving tray 520 a is in an open position extending from the heater/optical module 500 a which has the cover 28 attached. The receiving tray 520 b is in a closed position. Advantageously, in some embodiments the receiving trays 520 a, 520 b may allow easy placement of the microfluidic cartridge 200, by a user or by an auto-loading device. Such a design may also accommodate multiplexed pipetting of samples using the robotic fluid dispenser 400.

As illustrated in FIG. 1C, a recessed bay 524 can be a portion of the receiving tray 520 that is configured to selectively receive the microfluidic cartridge 200. The cartridge 200 may be aligned in the recessed bay 524 of the receiving tray 520 so that various components of the apparatus 10 that can operate on the microfluidic cartridge 200 (such as, heat sources, detectors, force members, and the like) are positioned to properly operate on the microfluidic cartridge 200 while the cartridge 200 is received in the recessed bay 524 of the receiving tray 520. For example, contact heat sources on the heater substrate 600 (not shown) may be positioned in the recessed bay 524 such that the heat sources can be in thermal communication with distinct locations on the microfluidic cartridge 200.

The cartridge 200 may include a label 204 attached to the top side of the cartridge 200. The label 204 may include a window portion 210 through which the detection chambers may be optically accessible by the detector head as discussed in further detail below, for the detection of target nucleic acids, e.g., target amplicons.

Microfluidic Cartridges

FIG. 2 is a top plan view of a microfluidic cartridge 200. Certain embodiments contemplate that one or more samples may be introduced into the microfluidic cartridge 200 to undergo analysis. The diagnostic analysis may include thermocycling of the sample to effectuate nucleotide amplification, such as by PCR, of one or more target polynucleotides from one or more samples and may include the detection of amplified target nucleic acids in the sample.

The term “cartridge,” as used herein, refers to a unit that may be disposable, or reusable in whole or in part, and that can be configured to be used in conjunction with some other apparatus that has been suitably and complementarily configured to receive and operate on (such as deliver heat, light, and the like, to) the cartridge. By microfluidic, as used herein, is meant that volumes of sample, and/or reagent, and/or amplified polynucleotide are from about 0.001 μl to about 999 μl, such as from 1-100 μl, or from 2-25 μl, as defined above. Similarly, as applied to a cartridge, the term microfluidic means that various components and channels of the cartridge, as further described herein, are configured to accept, and/or retain, and/or facilitate passage of microfluidic volumes of sample, reagent, or amplified polynucleotide. Certain embodiments herein can also function with nanoliter volumes (in the range of 10-500 nanoliters, such as 100 nanoliters).

The cartridge 200 may comprise a plurality of sample lanes. The microfluidic cartridge 200 shown in FIG. 2 includes twelve independent sample lanes 300 a-l. However, the skilled artisan will appreciate that the cartridge shown in FIG. 2 is exemplary, and that the present embodiments encompass cartridges that have 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, or more, sample lanes. The microfluidic cartridge 200 may can be configured so that sample analyses can be carried out in two or more of the sample lanes in parallel, for example simultaneously, and wherein each sample lane 300 a-l may be independently associated with a given sample. The samples to be analyzed in each sample lane 300 a-l may be the same as, or different, from one another. Each sample lane 300 a-l can be configured to carry out amplification on a sample in which the presence or absence of one or more target polynucleotides can be determined.

As described in more detail below with relation to FIG. 3 , each sample lane 300 a-l may include a microfluidic network having an inlet, microfluidic valves, microfluidic gates, channels, and reaction chambers, such as one or more amplification chambers, and a plurality of detection chambers. Each sample lane 300 a-l can be conceptually divided into a first stage 206 and a second stage 208. The microfluidic cartridge 200 may include a registration member 202, for example, a cutout, which corresponds to a complementary edge 526 in the recessed bay 524 of the receiving tray 520 a, 520 b of the heater/optical modules 500 a, 500 b. The pairing of the registration member 202 of the microfluidic cartridge 200 and the complementary edge 526 of the recessed bay 524 allows for secure and correct placement and orientation of the microfluidic cartridge 200 in the receiving tray 520 a, 520 b.

A microfluidic cartridge 200 may be constructed from a number of layers. Accordingly, one aspect of the present embodiments relates to a microfluidic cartridge that comprises a first, second, third, fourth, and fifth layers wherein one or more layers define a plurality of microfluidic networks, each network having various components configured to carry out amplification and detection on a sample in which the presence or absence of one or more polynucleotides is to be determined. In another embodiment, the microfluidic cartridge 200 can comprise a plurality of lanes, each including a reaction chamber, etched or molded in a single plane, such as in a molded plastic substrate, with each lane being closed by a cover layer, such as an adhesive plastic film layer. Embodiments with 1, 2, 4, 6, 8, 10, 12, 14, 16, 18, 20, 22, 24, 28, 30, or more lanes per cartridge are contemplated. For example, one suitable design is a single cartridge 200 having 12 sample lanes, each lane having an amplification chamber and six detection chambers.

In understanding the relative orientation of the cartridge 200, a sample lane 300 can be considered a column on the cartridge 200, running along a y-axis and multiple lanes 300 a-1 can be aligned side by side, in the direction of an x-axis. In certain embodiments disclosed herein, the x and y axes designated for the cartridge 200 may correspond to the x and y axes designated for the diagnostic apparatus 10 in FIGS. 1A-C, such that a relative spatial orientation of the cartridge 200 when it is positioned in the diagnostic apparatus 10 is understood.

FIG. 3 shows a single sample lane 300 in a microfluidic cartridge, e.g., microfluidic cartridge 200, shown in FIG. 2 . The sample lane 300 comprises a microfluidic network, the microfluidic network including an inlet 302, microfluidic valves 330 a, 330 b, 370 a, and 370 b, microfluidic gates 310 a and 310 b, microfluidic channels 360, 364, 366, and 374, an amplification chamber 362, and six detection chambers 372 a-f.

The spatial arrangement of the sample lane shown in FIG. 3 can be maintained, such that the sample lane 300 constitutes a column along the y-axis. In this manner, the sample lane 300 can be comprised of three columns of detection chambers (a first column of detection chambers 372 a and 372 d; a second column of detection chambers 372 b and 372 e; and a third column of detection chambers 372 c and 372 f). Likewise, the sample lane 300 can be comprised of two rows of detection chambers (a bottom row of detection chambers 372 a-372 c and a top row of detection chambers 372 d-372 f). Accordingly, in the embodiment shown in FIG. 3 , there are six detection chambers within the sample lane 300. The skilled artisan will appreciate, however, that the sample lane shown in FIG. 3 is exemplary, and that the embodiments disclosed herein can have fewer, or more, detection chambers within a sample lane, e.g., 2, 4, 6, 8, 10, 12, 14, 16, or more.

In the microfluidic network of the sample lane 300, the inlet 302 is the point at which a sample is input by the fluid dispenser 400 into the microfluidic network. The various components of the microfluidic network are spatially arranged in the sample lane 300 such that the inlet 302 can be considered the most upstream portion of the microfluidic network, meaning that in the progression of fluidic movement throughout the microfluidic network, all other components can be downstream of the inlet 302. The vent 368 and 376 are the most downstream components of the microfluidic network, meaning that in the progression of fluidic movement throughout the microfluidic network of the sample lane 300, the vents 368 and 376 are the components in the microfluidic network that are reached last as the fluid travels in the varying paths of the microfluidic network.

The inlet 302 can be manufactured to be frustoconical in shape with an appropriate conical angle so that industry-standard pipette tips (e.g., 2 μl, 10 μl, 20 μl, 200 μl, volumes, etc.) fit snugly, entering from the widest point of the inlet. Thus, in certain embodiments, an inlet comprises an inverted frustoconical structure of at least 1 mm height, and having a diameter at its widest point that accepts entry of a pipette tip, of from 1-5 mm. The apparatus herein may be adapted to suit other, later-arising, industry standards for pipette tips not otherwise described herein. Typically the volume of sample accepted via an inlet into a microfluidic network in a sample lane is from 0.1-20 μl, e.g., 5-10 μl. The fluid dispenser 400 can used to appropriately place the pipette tip in the inlet 302 of the sample lane 300. The inlet hole can be designed to fit a pipette tip snugly and to create a good seal around the pipette tip, within the cone of the inlet hole. Once the pipette tip lands within the cone, the conical shape guides the pipette and mechanically seals the combination to provide error free dispensing or withdrawal of fluid into the cartridge 200. However, the cone is designed such that the sealing is reversible to avoid pulling the cartridge 200 away from the recessed bay 524 in the receiving tray 520, when the pipette tips are lifted after completion of the dispensing operations.

As part of the first stage 206, the microfluidic network extends downstream from the inlet 302 along the first channel 360. The first channel 360 extends past, and is in fluid communication with, the amplification gate 310 a and the amplification valve 330 a. Downstream of the amplification gate 310 a and the amplification valve 330 a, the first channel can extend to, and be in fluid communication with, the amplification chamber 362. The second channel 364, which can be in fluid communication with the amplification chamber 362, can extend from the amplification chamber 362 through the second amplification gate 310 b and through the first detection valve 370 a, in the second stage 208 of the sample lane 300. In this manner, the second channel 364 extends from the first stage 206 of the microfluidic network of the sample lane 300 to the second stage 208. In the first stage 206, the third channel 366 is in fluid communication with the second channel 364 and can extend downstream from the second channel 364 at a point upstream of the second amplification gate 310 b. The third channel 366 can be in fluid communication with the second amplification valve 330 b and can extend from the second channel 364 to the first vent 368, and can be in fluid communication with the first vent 368.

In the second stage 208 of the microfluidic network, the second channel 364 can extend downstream through, and be in fluid communication with, the first detection valve 370 a. Extending past the first detection valve 370 a, the second channel 364 can split into two subchannels 365 a and 365 b, both of which are in fluid communication with the second channel 364. The subchannels 365 a, 365 b can each split again into additional subchannels 365 a 1-3 and 365 b 1-3, respectively. Subchannels 365 a 1-3 can extend through, and can be in fluid communication with, the detection chambers 372 a-c, respectively. Likewise, subchannels 365 b 1-3 can extend through, and be in fluid communication with, the detection chambers 372 d-f. Extending from detection chambers 372 a-c, subchannels 365 a 1-3 can connect together again downstream of the detection chambers 372 a-c as subchannel 367 a. Extending from detection chambers 372 d-f, subchannels 365 b 1-3 can connect together again downstream of the detection chambers 372 d-f as subchannel 367 b. Further downstream, subchannels 367 a and 367 b can connect together to form a fourth channel 374, which can extend to, and be in fluid communication with, the second vent 376. Along the fourth channel 374, upstream of the second vent 376, can be positioned a second detection valve 370 b in fluid communication with the fourth channel 374. The vents 368 and 376 may be configured to drain excess sample from the microfluidic network and prevent a user from introducing any excess amount of liquid into the microfluidic cartridge 200.

The amplification chamber 362 can have a volume of about 5-10 μl, and particular embodiments of the amplification chamber 362 have a volume of about 8 μl. For amplification chambers of about 8 μl, the input volume of the sample can be approximately 10 μl. Sample input volumes may be greater than the volume of the amplification chamber 362 in order to account for sample volumes located in the channels and detection chambers 372 a-f. Excess volume may also be drained from the microfluidic network through the vents 368 and 376.

In certain embodiments, the detection chambers 372 a-f can each have a volume of about 1 μl. In some embodiments, the detection chambers 372 a-f are of a volume equal to each other. In some embodiments, the detection chambers 372 a-f may be of varying volumes. The detection chambers 372 a-f may individually be of a volume less than the volume of the amplification chamber 362. In some embodiments, the detection chambers 372 a-f may collectively be of a volume less than the volume of the amplification chamber 362.

In some embodiments, the inside walls of the channels in the amplification chamber 362 and detection chambers 372 a-f can be made very smooth and polished to a shiny finish (for example, using a polish such as SPI A1, SPI A2, SPI A3, SPI B1, or SPI B2) during manufacture. The amplification chamber 362 and detection chambers 372 a-f may be polished in order to minimize any microscopic air trapping in the surface of the chambers, which may cause bubbling during thermocycling. The presence of bubbles, particularly in the detection chambers 372 a-f might cause a false reading. Furthermore, the amplification 362 and detection chambers 372 a-f can be made shallow such that the temperature gradient across the depths of the chambers is minimized.

Turning now to FIG. 4A, FIG. 4A is a representation of an exemplary amplification valve, e.g., the first amplification valve 330 a, shown in the microfluidic network of FIG. 3 . A valve is a component of the microfluidic network that can be set in an initial open state, and thus, when open, allowing a sample containing polynucleotides to pass along a channel from a position on one side of the valve (e.g., upstream of the valve) to a position on the other side of the valve (e.g., downstream of the valve). It is noted that the other valves in the microfluidic network (such as, the second amplification valve 330 b and the first and second detection valves 370 a and 370 b) can be provided with the same structure and can operate in a manner similar to the first amplification valve 330 a, as described herein.

As shown in FIG. 4A, the valve 330 a can include a valve loading port 332, a valve loading channel 334, and a valve junction 336. The valve junction 336 is the point where the valve loading channel 334 of the first amplification valve 330 a intersects the first channel 360. Sections of the first channel 360 shown in FIG. 4A are, in spatial relation to the first amplification valve 330 a, an upstream side 338 of the first channel 360 and a downstream side 340 of the first channel 360.

As shown in FIGS. 4B and 4C, the valve 330 a may include one or more masses of a thermally responsive substance (TRS) 345 that is substantially immobile in the valve loading channel 334 at a first temperature and more mobile at a second temperature. A mass of TRS can be an essentially solid mass or an agglomeration of smaller particles that cooperate to obstruct the passage upon actuation. Examples of TRS's 345 include a eutectic alloy (e.g., a solder), wax (e.g., an olefin), polymers, plastics, and combinations thereof.

The TRS 345 can be deposited into the loading port 332 machined in the microfluidic substrate of the microfluidic cartridge 200. The loading port 332 of the microfluidic cartridge 200 can be dimensioned in such a way that a droplet of TRS can be accurately propelled to the bottom of the loading port 332 using, for example, compressed air. The microfluidic cartridge 200 can be maintained at a temperature above the melting point of the TRS thereby permitting the TRS to stay in a molten state immediately after it is dispensed. After the drop falls to the bottom of the loading port 332, the molten TRS 345 is drawn into the valve loading channel 334 by capillary action. The amount of TRS 345 that is dispensed into the loading port 332 can be approximately equal to the volume of the valve loading channel 334. The valve loading channel 334 can be structured so that even though the TRS 345 dispensed into the loading port 332 may vary between a minimum and a maximum dispensed amount, the TRS always fills up to, and stops at, the valve junction 336 because the junction 336 provides a higher cross section than that of the loading channel 334 and thus reduces the capillary forces. When the microfluidic cartridge 200 is cooled to a first temperature, the mass of immobile TRS is situated in the valve loading channel 334, not blocking the first channel 360 at the valve junction 336.

FIG. 4B shows the first amplification valve 330 a in the initial open state, which permits the sample 350 to travel through the first channel 360 from the upstream side 338 of the valve 330 a to the downstream side 340 of the valve 330 a. Upon actuation, e.g., by application of heat to the first amplification valve 330 a, the valve 330 a can transition from an open state to a closed state.

FIG. 4C shows the first amplification valve 330 a in a closed state, such that upon heating, at least a portion of the TRS 345 has moved from the loading channel 334 into the valve junction 336. The valve 330 a operates by heating the TRS and air trapped in the loading port 332. The expansion of the heated air in the loading port 332 forces the mobile TRS 345 forward in a manner so that it moves into the valve junction 336. As the TRS 345 once again cools and solidifies it becomes immobile again and can thereby block the passage of the sample 350 in the first channel 360, preventing that portion of the sample 350 from traveling from the upstream side 338 of the valve 330 a to the downstream side 340 of the valve 330 a.

FIG. 5 is a representation of an exemplary amplification gate, e.g., the first amplification gate 310 a, shown in the microfluidic network of FIG. 3 . A gate is a component of a microfluidic network that, unlike a valve, can be set in an initially closed state, meaning that the gate can initially act to prevent a sample from passing to the downstream portion of the channel with which the gate is in fluid communication. Upon opening, the amplification gate 310 a can then allow the passage of the sample to the downstream portion of the channel. It is noted that the second gate 310 b of the microfluidic network can be provided with the same structure and can operate in a manner similar to the first amplification gate 310 a, as described herein.

As shown in FIG. 5 , the gate 310 a can be comprised of a loading port 314, a gate loading channel 312, and a gate junction 316. The gate junction 316 is the point where the gate loading channel 312 of the first amplification gate 310 a intersects with the first channel 360. Shown in FIG. 5 are the upstream portion 318 and the downstream portion 320 of the first channel 360.

A mass of TRS 345 can be deposited into the loading port 314 and passed into the gate loading channel 312. The loading port 314 and the gate loading channel 312 can be dimensioned in such a way that the deposited TRS 345 does not become immobilized in the gate loading channel 312, but extends into the gate junction 316. In some embodiments, the gate junction 316 can be narrower (e.g., approximately 150 μm wide and 100 μm deep) than the upstream 318 and downstream 320 portions of the first channel 360 with which it is in fluid communication. An upstream side 318 as well as a downstream side 320 of the gate junction 316 can be made wide (e.g., approximately 500 μm) and deep (e.g., approximately 500 μm) to help ensure the wax stops at the gate junction 316.

During operation of the diagnostic apparatus 10, a heater may be positioned external to the cartridge 200 and may be in thermal communication with the gate 310 a. At the required time during operation of the diagnostic apparatus, the external heater may be used to melt the TRS 345 in gate 310 a. The melted TRS 345 may be pushed downstream by upstream fluidic pressure and may move downstream along with the sample 350. The amount of TRS 345 melted and moved out of the gate junction 316 may be minimized for optimal gate 310 opening.

In various embodiments, the gate 310 a can be configured to minimize the effective area or footprint of the gate within the network, such as by being bent as shown in FIG. 3 and FIG. 5 . Minimizing the effective area or footprint of the gate within the network can increase the density of a given microfluidic network and can thereby reduce the cost per part, provide for a more compact network, and minimize network channel length or volume.

Fluid Dispensers

As mentioned above, the devices disclosed herein can include fluid dispensers. Turning to FIG. 6 , shown is an interior view of the diagnostic apparatus 10 with the fluid dispenser 400 positioned over the cartridge 200. The microfluidic cartridge 200 is configured to receive sample(s) via the one or more inlets 302, delivered by a fluid dispenser 400. A liquid dispenser 400 for use with the diagnostic apparatus 10 herein is described in U.S. patent application Ser. No. 12/212,403, filed Sep. 17, 2008, and incorporated herein by reference in its entirety.

In various embodiments, preparation of an amplification-ready sample in the diagnostic apparatus 10 can include one or more of the following steps: contacting a polynucleotide sample from the sample tube 32 with an amplification reagent mixture in one or more of the containers in the holder 26, the reagent mixture comprising a polymerase enzyme and a plurality of nucleotides (in some embodiments, the amplification reagent mixture can further include a positive control polynucleotide and a fluorogenic hybridization probe selective for at least a portion of the portion); in some embodiments, the amplification reagent mixture can be in the form of one or more lyophilized pellets, as stored in a receptacle on a holder, and the method can further include reconstituting the pellet with liquid to create an amplification reagent mixture solution. Various, such as one or more, of the liquid transfer operations associated with the foregoing steps can be accomplished by the automated fluid dispenser 400, having multiple pipette tips 402, under control of a microprocessor (not shown). As discussed below, in some embodiments, reagents, buffers, etc. used in the preparation of an amplification-ready sample are disposed within the microfluidic cartridge itself, e.g., within the amplification chamber. The dispenser can introduce the sample into the microfluidic network, where the sample is mixed with reagents, etc., within the network.

The fluid dispenser 400 can be configured to dispense a solution (e.g., of a prepared sample, amplification reagents, and probes, etc.) into the microfluidic cartridge 200. The fluid dispenser 400 can be configured to travel from a first set of positions above the rack 24 and holders 26 having various containers that hold reagents, etc., to a second set of positions above the cartridge 200, where pipette tips 402 can be inserted into the inlets 302 of the microfluidic cartridge 200. The cartridge 200 can be positioned in the receiving tray 520. The second set of positions is depicted schematically in FIG. 6 . The fluid dispenser 400 can travel between the first set of positions and the second set of positions by motion in two orthogonal directions in a horizontal plane along the lateral rail 20 (x-axis, of FIG. 1B) and fore-aft rail 22 (y-axis) of the gantry 18 and in a vertical direction (z-axis) to reach the holders 26 and the cartridge 200. Multiple, e.g., 4, pipette tips 402 can dispense fluid into inlets 302 of the microfluidic cartridge 200.

In some embodiments, the fluid dispenser 400 can be configured to accept or dispense, in a single operation, an amount of 1.0 ml of fluid or less, such as an amount of fluid in the range 10 nl-1 ml. Specifically, the fluid dispenser 400 can accept and dispense, in a single operation, an amount of about 5-15 μl of the sample. When transferring a sample containing extracted nucleic acid from a pipette tip 402 to an inlet 302 on the microfluidic cartridge 200, for example, using the fluid dispenser 400, a volume of air or other gas can also be introduced into the microfluidic network of the sample lanes 300 to provide propulsion or downstream movement to the sample. The volume of air or gas introduced into the microfluidic network can be between about 0.5 ml and about 5 ml, but depending on the volume of the pipette tip 402 and the volume of air or gas required for movement of the sample within the microfluidic network.

Heater/Optical Modules

FIGS. 7A-C illustrate the heater/optical module 500 of the detection apparatus 10 found in certain embodiments. The heater/optical module 500 may comprise an optical unit 502 and a receiving tray 520 or a portion of the receiving tray. FIG. 7A shows one embodiment of the enclosed optical unit 502 having a motor 504 externally attached thereto for driving movement of a detector head 700. The detector head 700 may be housed inside the optical module 502. FIG. 7A illustrates the empty receiving tray 520 coupled to a bottom side 506 of the optical unit 502. The receiving tray 520 and the optical unit 502 together comprise the heater/optical module 500. The receiving tray 520 may receive a cartridge 200 in a recessed bay 524, the cartridge 200 itself receiving samples upon which amplification and detection can be performed. For example, the recessed bay 524 can have an edge 526 which is complementary in shape to the registration member 202 on the microfluidic cartridge 200 so that the microfluidic cartridge 200 is selectively received in, e.g., a single orientation. The registration member 202 can be, for example, a cut-out on an edge of the cartridge 200 or one or more notches that are made on one or more of the sides. By selectively receiving the cartridge 200, the recessed bay 524 can help a user to position the cartridge 200 so that the optical module 502 can properly operate on the cartridge 200. In this way, error-free alignment of the cartridges 200 can be achieved.

After receiving the samples, the receiving tray 520 may be moved (e.g., mechanically or manually) on rails 522 to a position underneath the optical unit 502. In some embodiments, the receiving tray 520 may comprise an auto-loading device, which automatically aligns the cartridge once positioned beneath the optical module 502. In some embodiments, the recessed bay 524 of the receiving tray 520 may contain a heater substrate 600 which can be in thermal or physical communication with the cartridge 200 to activate certain cartridge components and conduct the thermal cycling necessary for nucleotide amplification and detection. In some embodiments, the receiving tray 520 may subsequently be raised to place the cartridge 200 in thermal and/or physical contact with the optical unit 502, such as in contact with an aperture plate 540 on the bottom side 506 of the optical unit 502.

FIG. 7B illustrates an embodiment of the optical unit 502 with a front panel 508 removed to show the interior of the optical unit 502. Shown in FIG. 7B is the detector head 700. As described in detail below, movement of the detector head 700 may be driven by the motor 504 to move laterally across the interior of the optical unit 502 to provide optical scanning and detection on the cartridge 200 when the cartridge 200 is positioned below the optical module 502 in the receiving tray 520. Shown in FIG. 7B is an aperture plate 540, positioned at the bottom side 506 of the optical unit 502.

FIG. 7C provides a bottom plan view of the optical unit 502. Shown in FIG. 7C is the aperture plate 540 and a normalizer plate 546 attached to the bottom side 506 of the optical module 502. The normalizer plate 546 may be used to calibrate the light source-photodetector pairs of the detector head 700. The normalizer plate 546 preferably comprises one or more components having known, standardized optical characteristics, and is configured to calibrate, standardize, and/or confirm proper operation of the detector head 700 and associated detector pairs and optical unit 502 circuitry. In some embodiments, prior to the start of the detection process, the detector head 700 can be positioned over the normalizer plate 546 and calibrated using the known properties of the normalizer plate 546. The specific light sources in the detector head 700 can be activated to shine light on corresponding portions of the normalizer plate 546. The light can be reflected back from the normalizer plate 546 to the detector (e.g. photodiode) associated with the light source of the detector pair. The light transmission received by the light detector can be recorded and compared with the known value of the optical characteristics of the normalizer plate 546. If the recorded values and known values do not correlate, corrective action may be taken, such as including an offset in the measurements or notifying the user of the error. In some embodiments, the normalizer plate 546 may be made of optically-transparent material such as polycarbonate mixed with a highly fluorescent dye, or other standardized chromophore or fluorophore. In one embodiment, the normalizer plate includes a standardized chromophore or fluorophore for each channel or color for detection by the detector head 700.

As shown in FIG. 7C, the aperture plate 540 contains apertures 557. The dimensions of apertures 557 are such that the detector's light sources and photodetectors may have access to (optically excite or view) the contents in the cartridge 200's detection chambers when the detector is moved to a plurality of positions within optical unit 502. For example, when a light source-photodetector pair of the detector 700 is located in a position over a particular aperture 557, light may travel from the light source and reach the detection chamber in the cartridge 200 through the aperture 557. The fluorescing reagents in the detection chamber may then be visible to the photodetector via the aperture 557.

FIG. 8 illustrates a cross-section of the detector head 700 taken along line 8 of FIG. 7B. The detector head 700 may be configured to optically excite and/or monitor fluorescence emitted in connection with detection of target polynucleotides present in the reaction chambers in the cartridge 200, such as the amplification chambers 362 and/or detection chambers 372 a-f. Note that a positive result (presence of a target amplicon) may be indicated by increased fluorescence or decreased fluorescence, depending on assay design. For example, when the assay involves a fluorophore and a quencher, the quencher may quench fluorescence when the target is present, or in other assay designs, when the target is absent.

The device may comprise a plurality of detector pairs, e.g., 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, or more, such as the light source-photodetector pair 726. Each detector pair 726 can be comprised of a light source 726 a, such as a light-emitting diode (LED), and a corresponding light detector 726 b, such as a photodiode. The light source 726 a may selectively emit light in an absorption band of a fluorescent moiety, and the light detector 726 b may selectively detect light in an emission band of a fluorescent moiety.

In certain embodiments the light source 726 a may comprise a bandpass-filtered diode that selectively emits light in the absorption band of the fluorescent probe. Light detector 726 b may comprise a bandpass filtered photodiode that selectively detects light in the emission band of the fluorescent probe. In certain embodiments, a filter 726 a 1, such as a bandpass filter may be applied to the light source 726 a's light. The light from the light source 726 a passes through a filter before passing through the sample in the reaction chambers. In certain embodiments, the optical path-length for the light from the reaction chamber to the light detector 726 b may be very small. The incident light from light source 726 a generates fluorescence in the reaction chambers. Light from the reaction chamber then travels to the light detector 726 b. Certain embodiments seek to mitigate any undesired light from entering the detector and thereby adversely affecting the light signal from the reaction chamber.

For the sake of explanation, a collection of cartridges or detector pairs along the length (x-axis) of the cartridge are referred to as a “row” and those along the width (y-axis) are referred to as a “column.” In some embodiments, two or more detector pairs, for example detector pairs 726 and 727 in FIG. 8 , may be arranged side by side collinearly in the detector head 700 as a column. In some embodiments, each one of the plurality of detector pairs, or a column of detector pairs, may be arranged along the length of the detector head 700 in rows. For example, behind the detector pairs 726 and 727 illustrated in FIG. 8 may be another column of detector pairs arranged in a similar or the same orientation. Certain embodiments contemplate six or more columns of such detector pairs, having two or more detector pairs in each column. For example, in some embodiments, there would be 12 detector pairs in total (two rows and six columns) with two detector pairs per column, permitting simultaneous detection of samples within 12 separate detection chambers.

Each light source, such as, for example, light source 726 a, may be configured to produce light of a wavelength specific to a specific fluorescent moiety contained in a reaction chamber, e.g. a detection chamber. Each light detector, such as for example 726 b, may be configured to detect the light emitted from the fluorescent moieties associated with the light produced by the light emitter in the detector pair. The detector pairs may be configured to independently detect a plurality of fluorescent moieties having different fluorescent emission spectra, wherein in each reaction chamber (e.g., detection chamber), emission from each fluorescent moiety can be tracked and correlated to the presence or absence of one particular target polynucleotide. Although folded light paths can be used, one embodiment utilizes a detector and emitter pair where each is in direct optical contact with the reaction (detection) chamber, preferably simultaneously in such contact. Optionally, the photodetector and light source of a detector pair are aligned with the reaction chamber along lines that substantially intersect at an acute angle at the reaction chamber. The angle can be, for example, between about 5 and 70 degrees, preferably between about 8 and 60 degrees, more preferably between about 10 and 50 degrees.

FIG. 8 also illustrates the plating arrangement found in certain embodiments of the diagnostic apparatus 10's heater optical/module 500 and the associated receiving tray 520 and heater substrate 600 of the cartridge 200. When the cartridge 200 is brought within proximity of the aperture layer 540 of the optical module 502, the heater substrate 600, the cartridge 200, and aperture layer 540 may be situated as depicted in the embodiment of FIG. 8 . For simplicity sake, not shown in FIG. 8 is the receiving tray 520, in which the heater substrate 600 may be housed. As discussed above, the cartridge 200 may comprise a plurality of reaction chambers, which may be located so as to be thermally controlled separately from one another, or in groups. As discussed above, the heater substrate 600 may comprise a plurality of heaters. The aperture plate 540 may provide pressure to the cartridge 200 as a force member (not shown) pushes the receiving tray 520 upwards, in order to facilitate heating and cooling by heater substrate 600.

In certain embodiments, the receiving tray 520 places the cartridge 200 in proximity to the heater substrate 600 or aperture layer 540, but does not mechanically couple and/or thereby place the layers in contact with one another. In this manner, the cartridge 200 may be thermally, but not mechanically, coupled to the heater substrate 600. In other embodiments, the receiving tray 520 places the heater substrate 600 in both mechanical and thermal contact with the cartridge 200 and the cartridge 200 in mechanical contact with the aperture layer 540. In various embodiments, the apparatus may include one or more force members (not shown) that are configured to apply pressure to the receiving tray 520 in order to thermally couple the heat sources in the heater substrate 600 to the microfluidic cartridge 200 positioned in the receiving tray 520. The application of pressure may be important to ensure consistent thermal contact between the heater substrate and the reaction chambers, gates, and valves, etc., in the microfluidic cartridge 200. When the receiving tray 520 is in a closed position, thereby being positioned under the aperture plate 540 of the optical unit 502, the force member, such as a motor assembly, positioned below the receiving tray 520 may begin traveling upwards towards the bottom side 506 of the optical unit 502, thereby bringing the receiving tray 520 closer to the optical unit 502. As the receiving tray 520 travels upwards towards the optical unit 502, the cartridge 200 may begin to come in contact with the bottom surface 506 of the aperture plate 540. The cartridge 200 may continue traveling upward until a sufficient pressure is received on the cartridge 200. The aperture plate 540 may be configured to apply an equal pressure across all points of the top of the cartridge 200 and thus, may press the cartridge 200 against the heater substrate 600 with uniform pressure. The aperture plate 540 may be selected to possess properties which facilitate this operation. For example, the material selection of the aperture plate 540 may provide very little deflection of the cartridge 200, when the cartridge 200 is pressed against the aperture plate 540.

The application of uniform pressure of the cartridge 200 against the heater substrate 600 may allow for uniform heating for each of the components of the cartridge 200 when desirable. Although uniform pressure and contact may be obtained between the heaters in the heater substrate 600 and the components (valves, gates, chambers, etc.) of the microfluidic networks in the cartridge 200, the heaters are not necessarily activated simultaneously. Thus, in certain embodiments, application of even pressure does not necessarily result in equal heating of different components of the cartridge 200. In some embodiments, both the activation of a specific heater in the heater substrate 600 along with the pressure applied by the aperture plate 540 to the cartridge 200 activate a particular component of cartridge 200.

FIG. 9 shows a top plan view of an exemplary heater substrate 600, which can be positioned in the bottom of the recessed bay 524 of the receiving tray 520. In various embodiments, the components of the microfluidic network in the sample lane 300 of the cartridge 200 can be heated by thermally coupling them with the heaters in the heater substrate 600. For example, the heater substrate can be positioned to heat (and/or cool) reaction chambers such as amplification chambers or detection chambers within the microfluidic cartridge 200. More specifically, the heater substrate 600 can be configured to thermally cycle a sample mixture comprising amplification reagents and an amplification-ready polynucleotide, thereby creating the conditions suitable for creating amplicons from the amplification-ready sample. The heater substrate 600 can also be configured to thermally cycle a sample mixture in the detection chambers, e.g., in order to perform melt-curve analyses or the like.

In preferred embodiments, each heater in the heater substrate 600 can be a contact heater, such as a resistive heater (or network thereof), a radiator, a fluidic heat exchanger and a Peltier device, or the like. The contact heat source can be configured in the recessed bay 524 to be thermally coupled to one or more distinct locations of the microfluidic cartridge 200 received in the receiving tray 520, whereby the distinct locations are selectively heated (and/or cooled). The contact heat sources can each be configured in the heater substrate 600 to be independently thermally coupled to a different distinct location in a microfluidic cartridge 200 received in the receiving tray 520, whereby the distinct locations are independently heated. The contact heat sources can be configured to be in direct physical contact with distinct locations of a microfluidic cartridge 200 received in the receiving tray 520.

As illustrated in FIG. 9 , the heater substrate 600 can include one or more heater lanes 602, the number of which can correspond to the number of sample lanes 300 in the microfluidic cartridge 200. In some embodiments, the heater substrate 600 can include 12 heater lanes 602 to correspond to the 12 sample lanes 300 that may be in the microfluidic cartridge 200.

The heaters in a heater lane 602 may be divided conceptually into first stage heaters 606 and second stage heaters 608, to correspond to the first stage 206 and second stage 208 of the microfluidic cartridge 200. Among the heaters in the first stage 606 may be a first amplification gate heater 610 a, a second amplification gate heater 610 b, a first amplification valve heater 630 a, a second amplification valve heater 630 b, and an amplification chamber heater 662. Included in the second stage heaters 608 may be a first detection valve heater 670 a, a second detection valve heater 670 b, and detection chamber heaters 672 a-f.

When the microfluidic cartridge 200 is placed in the recessed bay 524 of the receiving tray 520, the various components (e.g., reaction chambers, valves, and gates) of the microfluidic networks in the sample lanes 300 of the cartridge 200 are aligned adjacent to, and above, the corresponding heaters in the heater substrate 600, and consequently can be in thermal contact with the corresponding heaters in the heater substrate 600. When the microfluidic cartridge 200 is placed in the recessed bay 524, the heaters of the heater substrate 600 may be in physical contact with the respective components. For example, the first amplification gate heater 610 a can be aligned adjacent to the first amplification gate 310 a; the second amplification gate heater 610 b can be aligned adjacent to the second amplification gate 310 b; the first amplification valve heater 630 a can be aligned adjacent to the first amplification valve 330 a; the second amplification valve heater 630 b can be aligned adjacent to the second amplification valve 330 b; and the amplification chamber heater 662 can be aligned adjacent to the amplification chamber 362. Similarly, the first detection valve heater 670 a may be aligned adjacent to the first detection valve 370 a; the second detection valve heater 670 b may be aligned adjacent to the second detection valve 370 b; and the detection chamber heaters 672 a-f may be aligned adjacent to the respective detection chambers 372 a-f.

In some embodiments, multiple heaters can be configured to simultaneously and uniformly activate to heat their respective corresponding cartridge components of the microfluidic network in the microfluidic cartridge 200. Each heater can be independently controlled by a processor and/or control circuitry used in conjunction with the apparatus 10 described herein. Generally, the heating of microfluidic components (gates, valves, chambers, etc.) in the microfluidic cartridge 200, is controlled by passing currents through suitably configured micro-fabricated heaters, as illustrated in FIG. 9 . Under control of suitable circuitry, the lanes 300 of a multi-lane cartridge can then be heated independently, and thereby controlled independently, of one another. Furthermore, as is described in more detail below, the individual valves 330 a, 330 b, 370 a, 370 b, gates 310 a, 310 b, amplification chamber 362, and detection chambers 372 a-f, in a sample lane 300 can be heated independently, and thereby controlled independently, of one another within a given sample lane 300. This can lead to a greater energy efficiency and control of the apparatus 10, because not all heaters are heating at the same time, and a given heater is receiving current for only that fraction of the time when it is required to heat.

The heater substrate 600 may also include one or more heat sensors. In order to reduce the number of sensors or heaters required to control the heaters in a heater lane 602, the heaters may be used to sense temperature as well as provide heat, and thereby obviate the need to have a separate dedicated sensor for each heater. For example, the impedance and/or resistance of some materials change with the surrounding temperature. Accordingly, the resistance of the heater/sensors may be used as an indication of temperature when the sensors are not being actively heated.

In some embodiments, the heaters in the heater substrate 600 may be designed to have sufficient wattage to allow the heaters to be grouped in series or in parallel to reduce the number of electronically-controllable elements, thereby reducing the burden on the associated electronic circuitry. Heaters that are grouped together in this manner would be operated under synchronized and substantially simultaneous control.

In some embodiments, the first and second amplification valve heaters 630 a, 630 b can be grouped and configured to operate under synchronized control. In some embodiments, the first and second amplification gate heaters 610 a, 610 b can be grouped and configured to operate under synchronized control. In some embodiments, the first and second amplification valve heaters 630 a, 630 b and the amplification chamber heater 662 can be grouped and configured to operate under synchronized control. In some embodiments, the first and second detection valve heaters 670 a, 670 b can be grouped and configured to operate under synchronized control. In some embodiments, the detection chamber heaters 672 a-f can be grouped and configured to operate under synchronized control. In some embodiments, the first and second detection valve heaters 670 a, 670 b and the detection chamber heaters 672 a-f can be grouped and configured to operate under synchronized control. In some embodiments, the first stage heaters 606 can be grouped and configured to operate under synchronized control. In some embodiments, the second stage heaters 608 can be grouped and configured to operate under synchronized control.

In some embodiments, different combinations of the detection chamber heaters 672 a-f can be grouped and configured to operate under synchronized control. For example, the detection chamber heaters on the same side of the second stage heaters 608 can be grouped and configured to operate under synchronized control. For example, in some embodiments, detection chamber heaters 672 a-c can be grouped and configured to operate under synchronized control. For example, in some embodiments, detection chamber heaters 672 d-f can be grouped and configured to operate under synchronized control.

In some embodiments, the detection chamber heaters on opposite sides of the second stage heaters can be grouped and configured to operate under synchronized control. For example, in some embodiments, the detection chamber heaters in a column, such as detection chamber heaters 672 a and 672 d, can be grouped and configured to operate under synchronized control. Similar grouping and configuring can be applied to heater groups including detection chamber heaters 672 b and 672 e and to heater groups including detection chamber heaters 672 c and 672 f. The detection heaters 672 a-f can be configured to operate individually and independently or they can be configured to operate in groups of two (pairs), three (thirds), four, five or six, etc., or the like.

In some embodiments, the heating in the heater substrate 600 can be controlled by periodically turning the current on and off to a respective heater with varying pulse width modulation (PWM), wherein pulse width modulation refers to the on-time/off-time ratio for the current. The current can be supplied by connecting a micro fabricated heater to a high voltage source (for example, 30V), which can be gated by the PWM signal. In some embodiments, the device includes 48 PWM signal generators. In some embodiments there will be two PWM signal generators associated with each reaction chamber. Operation of a PWM generator includes generating a signal with a chosen, programmable period (the end count) and granularity. For instance, the signal can be 4000 μs (micro-seconds) with a granularity of 1 μs, in which case the PWM generator can maintain a counter beginning at zero and advancing in increments of 1 μs until it reaches 4000 μs, when it returns to zero. Thus, the amount of heat produced can be adjusted by adjusting the end count. A high end count corresponds to a greater length of time during which the micro fabricated heater receives current and therefore a greater amount of heat produced.

In various embodiments, the operation of a PWM generator can also include a programmable start count in addition to the aforementioned end count and granularity. In such embodiments, multiple PWM generators can produce signals that can be selectively non-overlapping (e.g., by multiplexing the on-time of the various heaters) such that the current capacity of the high voltage power is not exceeded.

Multiple heaters can be controlled by different PWM signal generators with varying start and end counts. The heaters can be divided into banks, whereby a bank defines a group of heaters of the same start count.

Methods of Detecting Target Nucleic Acids

In another aspect, provided herein are methods of detecting an analyte, e.g., a target nucleic acid from a sample, using the devices disclosed herein. The devices disclosed herein can advantageously be used to simultaneously analyze a single sample or multiple samples, for a plurality of target polynucleotides. Specifically, the “two-stage” design of the microfluidic cartridge enables for the testing and detection of many more targets than, for example, was previously possible in microfluidic cartridges that have a “one stage” design, where amplification and detection occur in the same chamber.

As used herein, the term “sample” can refer to a clinical specimen or sample from one or any number of sources, including, but not limited to, bodily fluids (including, but not limited to, blood, urine, serum, lymph, saliva, anal and vaginal secretions, perspiration, peritoneal fluid, pleural fluid, effusions, ascites, and purulent secretions, lavage fluids, drained fluids, brush cytology specimens, biopsy tissue, explanted medical devices, infected catheters, pus, biofilms and semen) of virtually any organism, with mammalian samples, particularly human samples, and environmental samples (including, but not limited to, air, agricultural, water and soil samples) finding use in the invention. In addition, samples can be taken from food processing, which can include both input samples (e.g. grains, milk or animal carcasses), samples in intermediate steps of processing, as well as finished food ready for the consumer.

The microfluidic network in each sample lane 300 shown in FIG. 3 is advantageously configured to carry out amplification, such as by PCR, on an amplification-ready sample, such as one containing nucleic acids extracted that have been from a sample. Several methods of nucleic acid extraction useful in the embodiments disclosed herein are known in the art. Exemplary discussions of nucleic acid extraction can be found, for example, in U.S. patent application Ser. No. 12/172,214, filed Jul. 11, 2008, U.S. patent application Ser. No. 12/172,208, filed Jul. 11, 2008, and U.S. patent application Ser. No. 12/281,247, filed Nov. 16, 2005, all of which are incorporated herein by reference in their entirety.

An amplification-ready sample can be prepared by mixing the sample nucleic acids (e.g., extracted sample nucleic acids) with amplification reagents. In some embodiments, the mixing is not performed within the microfluidic network of a microfluidic cartridge. For example, in some embodiments, an amplification-ready sample is prepared by mixing sample nucleic acids and amplification reagents within a container in a reagent holder 26. In other embodiments, the amplification-ready sample is prepared within the microfluidic network, e.g., the sample nucleic acids are mixed amplification reagents within a mixing chamber of the microfluidic network. Regardless of whether the mixture of sample nucleic acids and reagents occurs within the microfluidic network or outside of the microfluidic network, e.g., in a container in a reagent holder 26, the sample nucleic acids are introduced into the microfluidic network via an inlet port 302. Dispensing of the sample (whether amplification-ready or not) into the microfluidic network can be achieved either manually, or, for example, by an automated dispenser 400.

As discussed above, an amplification-ready sample is prepared by mixing nucleic acids from the sample to be analyzed with amplification reagents to create an amplification-ready sample. For example, an amplification-ready sample may include an amplification reagent mixture comprising a polymerase enzyme, a positive control nucleic acid, a fluorescent moiety specific for the positive control nucleic acids, and a plurality of nucleotides, and at least one fluorescent moiety that is selective for a target polynucleotide sequence.

Amplification

In some embodiments, the sample to be analyzed is dispensed within the microfluidic network via inlet port 302 and moved through to amplification chamber 362 as described elsewhere herein. The amplification-ready sample is isolated within the amplification chamber 362 by closing the amplification valves 330 a, 330 b in the microfluidic network upstream and downstream of the amplification chamber 362, respectively. In some embodiments, this is achieved by heating a TRS 345 to seal one or more channels (e.g., the first and second channels 360, 364 that communicate with the amplification chamber 362. Once isolated in the amplification chamber 362, the device may be activated to thermal cycle the amplification-ready sample within the amplification chamber 362 as described elsewhere herein, to generate an amplified sample. Specifically, as described elsewhere herein, the amplification chamber 362 of the microfluidic network is in thermal communication with, or thermally coupled to, an external heat source (e.g, the heater substrate 600). Thermal cycling of the amplification-ready sample creates an amplified sample, which, when target nucleic acids are present in the sample under analysis, includes amplicons of the target nucleic acids, i.e., target amplicons.

In some embodiments, the sample or specimen is contacted with a set of amplification primers under standard PCR conditions. For a review of PCR technology, including standard PCR conditions, applied to clinical microbiology, see DNA Methods in Clinical Microbiology, Singleton P., published by Dordrecht; Boston: Kluwer Academic, (2000) Molecular Cloning to Genetic Engineering White, B. A. Ed. in Methods in Molecular Biology 67: Humana Press, Totowa (1997) and “PCR Methods and Applications”, from 1991 to 1995 (Cold Spring Harbor Laboratory Press). Non-limiting examples of “PCR conditions” include the conditions disclosed in the references cited herein, such as, for example, 50 mM KCl, 10 mM Tris-HCl (pH 9.0), 0.1% Triton X-100, 2.5 mM MgCl₂, with an annealing temperature of 72° C.; or 4 mM MgCl₂, 100 mM Tris, pH 8.3, 10 mM KCl, 5 mM (NH₄)₂SO₄, 0.15 mg BSA, 4% Trehalose, with an annealing temperature of 59° C., or 50 mM KCl, 10 mM Tris-HCl (pH 9.0), 0.1% Triton X-100, 2.5 mM MgCl₂, with an annealing temperature of 55° C., or the like.

In some embodiments, the amplification-ready sample is amplified within the amplification chamber 362 by the polymerase chain reaction (PCR). Generally, in PCR, a target polynucleotide sequence is amplified by reaction with at least one oligonucleotide primer or pair of oligonucleotide primers. In embodiments wherein the sample nucleic acids are amplified by PCR, the amplification ready sample minimally comprises template nucleic acid (except in the case of a negative control as described below) and oligonucleotide primers and/or probes in combination with suitable buffers, salts, and the like, and an appropriate concentration of a nucleic acid polymerase. As used herein, “nucleic acid polymerase” refers to an enzyme that catalyzes the polymerization of nucleoside triphosphates. Generally, the enzyme will initiate synthesis at the 3′-end of the primer annealed to the target sequence, and will proceed in the 5′-direction along the template until synthesis terminates. An appropriate concentration includes one that catalyzes this reaction in the presently described methods. Known DNA polymerases useful in the methods disclosed herein include, for example, E. coli DNA polymerase I, T7 DNA polymerase, Thermus thermophilus (Tth) DNA polymerase, Bacillus stearothermophilus DNA polymerase, Thermococcus litoralis DNA polymerase, Thermus aquaticus (Taq) DNA polymerase Pyrococcusfuriosus (Pfu) DNA polymerase, and the like.

In addition to the above components, the reaction mixture of the present methods includes primers, probes, and deoxyribonucleoside triphosphates (dNTPs). Usually the reaction mixture will further comprise four different types of dNTPs corresponding to the four naturally occurring nucleoside bases, i.e., dATP, dTTP, dCTP, and dGTP. In some of the embodiments disclosed herein, each dNTP will typically be present in an amount ranging from about 10 to 5000 μM, usually from about 20 to 1000 μM, about 100 to 800 μM, or about 300 to 600 μM.

As used herein, the terms “primer” and “probe” include, but are not limited to oligonucleotides or nucleic acids. The terms “primer” and “probe” encompass molecules that are analogs of nucleotides, as well as nucleotides. Nucleotides and polynucleotides, as used herein shall be generic to polydeoxyribonucleotides (containing 2-deoxy-D-ribose), to polyribonucleotides (containing D-ribose), to any other type of polynucleotide which is an N- or C-glycoside of a purine or pyrimidine base, and to other polymers containing nonnucleotidic backbones, for example, polyamide (e.g., peptide nucleic acids (PNAs)) and polymorpholino (commercially available from the Anti-Virals, Inc., Corvallis, Oreg., as NEUGENE™ polymers), and other synthetic sequence-specific nucleic acid polymers providing that the polymers contain nucleobases in a configuration which allows for base pairing and base stacking, such as is found in DNA and RNA.

In some embodiments, the “primers” or “probes” disclosed herein can contain locked nucleic acids (LNA). “Locked nucleic acids” (LNAs) are ribonucleotides which contain a methylene bridge which joins the 2′ oxygen of the ribose with the 4′ carbon (see FIG. 27 ). Braasch D. A. and Corey, D. R. (2001), Locked nucleic acids (LNA); fine-tuning the recognition of DNA and RNA. Chem. Biol. 8, 1-7, provide an overview of LNAs. This article is herein explicitly incorporated by reference in its entirety. LNAs are available commercially, for example, from the company Proligo, Boulder, Colo., USA. Phosphorothioates are also known to the person skilled in the art and may be ordered, for example, from MWG-Biotech AG, Ebersberg, Germany. Accordingly, in some embodiments, the “primers” or “probes” disclosed herein can include 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, or more LNAs.

The terms nucleotide and polynucleotide include, for example, 3′-deoxy-2′,5′-DNA, oligodeoxyribonucleotide N3′→P5′ phosphoramidates, 2′-O-alkyl-substituted RNA, double- and single-stranded DNA, as well as double- and single-stranded RNA, DNA:RNA hybrids, and hybrids between PNAs and DNA or RNA. The terms also include known types of modifications, for example, labels which are known in the art, methylation, “caps,” substitution of one or more of the naturally occurring nucleotides with an analog, internucleotide modifications such as, for example, those with uncharged linkages (e.g., methyl phosphonates, phosphotriesters, phosphoramidates, carbamates, etc.), with negatively charged linkages (e.g., phosphorothioates, phosphorodithioates, etc.), and with positively charged linkages (e.g., aminoalklyphosphoramidates, aminoalkylphosphotriesters), those containing pendant moieties, such as, for example, proteins (including nucleases, toxins, antibodies, signal peptides, poly-L-lysine, etc.), those with intercalators (e.g., acridine, psoralen, etc.), those containing chelators (e.g., metals, radioactive metals, boron, oxidative metals, etc.), those containing alkylators, those with modified linkages (e.g., alpha anomeric nucleic acids, etc.), as well as unmodified forms of the polynucleotide or oligonucleotide.

It will be appreciated that, as used herein, the terms “nucleoside” and “nucleotide” will include those moieties which contain not only the known purine and pyrimidine bases, but also other heterocyclic bases which have been modified. Such modifications include methylated purines or pyrimidines, acylated purines or pyrimidines, or other heterocycles. Modified nucleosides or nucleotides will also include modifications on the sugar moiety, e.g., wherein one or more of the hydroxyl groups are replaced with a halogen, an aliphatic group, or are functionalized as ethers, amines, or the like. Other modifications to nucleotides or polynucleotides involve rearranging, appending, substituting for, or otherwise altering functional groups on the purine or pyrimidine base which form hydrogen bonds to a respective complementary pyrimidine or purine. The resultant modified nucleotide or polynucleotide may form a base pair with other such modified nucleotidic units but not with A, T, C, G or U. For example, guanosine (2-amino-6-oxy-9-beta.-D-ribofuranosyl-purine) may be modified to form isoguanosine (2-oxy-6-amino-9-.beta.-D-ribofuranosyl-purine). Such modification results in a nucleoside base which will no longer effectively form a standard base pair with cytosine. However, modification of cytosine (1-.beta.-D-ribofuranosyl-2-oxy-4-amino-pyrimidine) to form isocytosine (1-s-D-ribofuranosyl-2-amino-4-oxy-pyrimidine) results in a modified nucleotide which will not effectively base pair with guanosine but will form a base pair with isoguanosine. Isocytosine is available from Sigma Chemical Co. (St. Louis, Mo.); isocytidine may be prepared by the method described by Switzer et al. (1993) Biochemistry 32:10489-10496 and references cited therein; 2′-deoxy-5-methyl-isocytidine may be prepared by the method of Tor et al. (1993) J. Am. Chem. Soc. 115:4461-4467 and references cited therein; and isoguanine nucleotides may be prepared using the method described by Switzer et al. (1993), supra, and Mantsch et al. (1993) Biochem. 14:5593-5601, or by the method described U.S. Pat. No. 5,780,610 to Collins et al. The non-natural base pairs referred to as κ and π., may be synthesized by the method described in Piccirilli et al. (1990) Nature 343:33-37 for the synthesis of 2,6-diaminopyrimidine and its complement (1-methylpyrazolo[4,3]-pyrimidine-5,7-(4H,6H)-dione. Other such modified nucleotidic units which form unique base pairs have been described in Leach et al. (1992) J. Am. Chem. Soc. 114:3675-3683 and Switzer et al., supra, or will be apparent to those of ordinary skill in the art.

The primers and/or probes are preferably between 10 and 45 nucleotides in length. For example, the primers and or probes can be at least 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 31, 32, 33, 34, 35, 36, 37, 38, 39, 40, 41, 42, 43, 44, 45, or more nucleotides in length. Primers and/or probes can be provided in any suitable form, included bound to a solid support, liquid, and lyophilized, for example. In some embodiments, the primers and/or probes include oligonucleotides that hybridize to a target nucleic acid sequence over the entire length of the oligonucleotide sequence. Such sequences can be referred to as “fully complementary” with respect to each other. Where an oligonucleotide is referred to as “substantially complementary” with respect to a nucleic acid sequence herein, the two sequences can be fully complementary, or they may form mismatches upon hybridization, but retain the ability to hybridize under stringent conditions or standard PCR conditions as discussed below. As used herein, the term “standard PCR conditions” include, for example, any of the PCR conditions disclosed herein, or known in the art, as described in, for example, PCR 1: A Practical Approach, M. J. McPherson, P. Quirke, and G. R. Taylor, Ed., (c) 2001, Oxford University Press, Oxford, England, and PCR Protocols: Current Methods and Applications, B. White, Ed., (c) 1993, Humana Press, Totowa, N.J.

As used herein, the term “substantially complementary” refers to the complementarity between two nucleic acids, e.g., the complementary region of the capture probe and the target sequence, and/or between the linker sequence of the capture probe and the complementary region of the competitor nucleic acid. The complementarity need not be perfect; there may be any number of base pair mismatches that between the two nucleic acids. However, if the number of mutations is so great that no hybridization can occur under even the least stringent of hybridization conditions, the sequence is not a substantially complementary sequence. When two sequences are referred to as “substantially complementary” herein, it is meant that the sequences are sufficiently complementary to the each other to hybridize under the selected reaction conditions. The relationship of nucleic acid complementarity and stringency of hybridization sufficient to achieve specificity is well known in the art and described further below in reference to sequence identity, melting temperature and hybridization conditions. Therefore, substantially complementary sequences can be used in any of the detection methods described herein. Such probes can be, for example, perfectly complementary or can contain from 1 to many mismatches so long as the hybridization conditions are sufficient to allow, for example discrimination between a target sequence and a non-target sequence. Accordingly, substantially complementary sequences can refer to sequences ranging in percent identity from 100, 99, 98, 97, 96, 95, 94, 93, 92, 91, 90, 89, 85, 80, 75 or less, or any number in between, compared to the reference sequence.

“Stringent conditions” or “high stringency conditions”, as defined herein, may be identified by those that: (1) employ low ionic strength and high temperature for washing, for example 0.015 M sodium chloride/0.0015 M sodium citrate/0.1% sodium dodecyl sulfate at 50° C.; (2) employ during hybridization a denaturing agent, such as formamide, for example, 50% (v/v) formamide with 0.1% bovine serum albumin/0.1% Ficoll/0.1% polyvinylpyrrolidone/50 mM sodium phosphate buffer at pH 6.5 with 750 mM sodium chloride, 75 mM sodium citrate at 42° C.; or (3) employ 50% formamide, 5×SSC (0.75 M NaCl, 0.075 M sodium citrate), 50 mM sodium phosphate (pH 6.8), 0.1% sodium pyrophosphate, 5×Denhardt's solution, sonicated salmon sperm DNA (50 μg/ml), 0.1% SDS, and 10% dextran sulfate at 42° C., with washes at 42° C. in 0.2×SSC (sodium chloride/sodium citrate) and 50% formamide at 55° C., followed by a high-stringency wash consisting of 0.1×SSC containing EDTA at 55° C.

“Moderately stringent conditions” may be identified as described by Sambrook et al., Molecular Cloning: A Laboratory Manual, New York: Cold Spring Harbor Press, 1989, and include the use of washing solution and hybridization conditions (e.g., temperature, ionic strength and % SDS) less stringent that those described above. An example of moderately stringent conditions is overnight incubation at 37° C. in a solution comprising: 20% formamide, 5×SSC (150 mM NaCl, 15 mM trisodium citrate), 50 mM sodium phosphate (pH 7.6), 5×Denhardt's solution, 10% dextran sulfate, and 20 mg/ml denatured sheared salmon sperm DNA, followed by washing the filters in 1×SSC at about 37-50° C. The skilled artisan will recognize how to adjust the temperature, ionic strength, etc. as necessary to accommodate factors such as probe length and the like.

The amplification-ready sample prepared in the first step of the methods of the embodiments disclosed herein further includes an aqueous buffer medium that includes a source of monovalent ions, a source of divalent cations, and a buffering agent. Any convenient source of monovalent ions, such as potassium chloride, potassium acetate, ammonium acetate, potassium glutamate, ammonium chloride, ammonium sulfate, and the like may be employed. The divalent cation may be magnesium, manganese, zinc, and the like, where the cation will typically be magnesium. Any convenient source of magnesium cation may be employed, including magnesium chloride, magnesium acetate, and the like. The amount of magnesium present in the buffer may range from 0.5 to 10 mM, and can range from about 1 to about 6 mM, or about 3 to about 5 mM. Representative buffering agents or salts that may be present in the buffer include Tris, Tricine, HEPES, MOPS, and the like, where the amount of buffering agent will typically range from about 5 to 150 mM, usually from about 10 to 100 mM, and more usually from about 20 to 50 mM, where in certain preferred embodiments the buffering agent will be present in an amount sufficient to provide a pH ranging from about 6.0 to 9.5, for example, about pH 6.0, 6.5, 7.0, 7.5, 8.0, 8.5, 9.0, or 9.5. Other agents that may be present in the buffer medium include chelating agents, such as EDTA, EGTA, and the like. In some embodiments, the reaction mixture can include BSA, or the like.

In preparing the reaction mixture, the various constituent components may be combined in any convenient order. For example, the buffer may be combined with primer, polymerase, and then template nucleic acid, or all of the various constituent components may be combined at the same time to produce the reaction mixture.

Alternatively, commercially available premixed reagents can be utilized in the methods disclosed herein according to the manufacturer's instructions, or modified to improve reaction conditions (e.g., modification of buffer concentration, cation concentration, or dNTP concentration, as necessary), including, for example, TAQMAN® Universal PCR Master Mix (Applied Biosystems), OMNIMIX® or SMARTMIX® (Cepheid), IQ&#8482; Supermix (Bio-Rad Laboratories), LIGHTCYCLER® FastStart (Roche Applied Science, Indianapolis, Ind.), or BRILLIANT® QPCR Master Mix (Stratagene, La Jolla, Calif.). In some embodiments, the reagents can be premixed and disposed within reaction chambers, e.g., amplification chambers and/or detection chambers, of the systems disclosed herein. In some embodiments, reagents can be lyophilized and predisposed within vessels in a reagent rack, or the like.

Following preparation of the reaction mixture, the reaction mixture can be subjected to primer extension reaction conditions (“conditions sufficient to provide polymerase-based nucleic acid amplification products”), i.e., conditions that permit for polymerase-mediated primer extension by addition of nucleotides to the end of the primer molecule using the template strand as a template. In many embodiments, the primer extension reaction conditions are amplification conditions, which conditions include a plurality of reaction cycles, where each reaction cycle comprises: (1) a denaturation step, (2) an annealing step, and (3) a polymerization step. In some embodiments, the reaction cycles do not include a specific amount of time allotted for annealing, but rather combine annealing and polymerization steps. The number of reaction cycles will vary depending on the application being performed, but will usually be at least 15, more usually at least 20, and may be as high as 60 or higher, where the number of different cycles will typically range from about 20 to 40. For methods where more than about 25, usually more than about 30 cycles are performed, it may be convenient or desirable to introduce additional polymerase into the reaction mixture such that conditions suitable for enzymatic primer extension are maintained.

The denaturation step comprises heating the reaction mixture to an elevated temperature and maintaining the mixture at the elevated temperature for a period of time sufficient for any double-stranded or hybridized nucleic acid present in the reaction mixture to dissociate. For denaturation, the temperature of the reaction mixture will usually be raised to, and maintained at, a temperature ranging from about 85 to 100° C., usually from about 90 to 98° C., and more usually from about 93 to 96° C., for a period of time ranging from about 3 to 120 sec, usually from about 3 sec.

Following denaturation, the reaction mixture can be subjected to conditions sufficient for primer annealing to template nucleic acid present in the mixture (if present), and for polymerization of nucleotides to the primer ends in a manner such that the primer is extended in a 5′ to 3′ direction using the nucleic acid to which it is hybridized as a template, i.e., conditions sufficient for enzymatic production of primer extension product. In this embodiment, the annealing and extension processes occur in the same step. The temperature to which the reaction mixture is lowered to achieve these conditions will usually be chosen to provide optimal efficiency and specificity, and will generally range from about 50 to 75° C., usually from about 55 to 70° C., and more usually from about 60 to 68° C., more particularly around 60° C. Annealing conditions will be maintained for a period of time ranging from about 15 sec to 30 min, usually from about 20 sec to 5 min, or about 30 sec to 1 minute, or about 30 seconds.

This step can optionally comprise one of each of an annealing step and an extension step with variation and optimization of the temperature and length of time for each step. In a two-step annealing and extension, the annealing step is allowed to proceed as above. Following annealing of primer to template nucleic acid, the reaction mixture will be further subjected to conditions sufficient to provide for polymerization of nucleotides to the primer ends as above. To achieve polymerization conditions, the temperature of the reaction mixture will typically be raised to or maintained at a temperature ranging from about 65 to 75° C., usually from about 67 to 73° C. and maintained for a period of time ranging from about 15 sec to 20 min, usually from about 30 sec to 5 min.

In some embodiments, the cycling can include a 15-minute initial denaturation at 95° C., which is performed only once, followed by a denaturation step at 95° C. for 1 second, and an annealing/elongation step at 60° C. for 25 seconds. This two-step cycle can be repeated multiple times, e.g., about 45 times. In some embodiments, a final elongation step can be added at 72° C. for 10 minutes.

In some embodiments, the cycling can include a 15-minute initial denaturation step at 95° C., is followed by multiple cycles (e.g., about 45 cycles) of: denaturation at 95° C. for 1 second, annealing at 60° C. for 9 seconds and elongation at 72° C. for 9 seconds. A final elongation step can be added of 72° C. for 10 minutes.

The person skilled in the art of nucleic acid amplification knows the existence of other rapid amplification procedures such as ligase chain reaction (LCR), transcription-based amplification systems (TAS), self-sustained sequence replication (3SR), nucleic acid sequence-based amplification (NASBA), strand displacement amplification (SDA) and branched DNA (bDNA) (Persing et al. (1993) Diagnostic Molecular Microbiology: Principles and Applications (American Society for Microbiology, Washington, D.C.). The scope of the embodiments disclosed herein is not limited to the use of amplification by PCR, but rather includes the use of any rapid nucleic acid amplification methods or any other procedures described herein that can be readily carried out on the systems disclosed herein.

Detection

Following amplification, the amplified sample is then moved within the microfluidic network to one or more detection chamber 372 a-f. In some embodiments, equal amounts of the amplified are moved to a plurality of detection chambers. For example, in some embodiments, equal volumes of the amplified sample are transferred into 2, 4, 6, 8, 10, 12, or more, detection chambers. Movement of the amplified sample within the microfluidic network is described elsewhere herein, and can comprise opening an amplification gate 310 a upstream from the amplification chamber 362. In some embodiments, the amplification gate 310 a comprises a TRS, and opening the gate comprises applying heat to the TRS. In some embodiments, heating a TRS within the amplification gate 310 a removes the TRS from an upstream channel, e.g., the first channel 360, in communication with the amplification chamber 362.

Fluidic pressure, e.g., pressure from discharging fluid or gas into the network, can be applied to the network, in order to facilitate movement of the amplified sample within the microfluidic networks. For example, the application of a fluidic pressure can be achieved by discharging a fluid (e.g., a gas or liquid), from a pipette into an inlet of the microfluidic network that resides upstream from the sample, thereby forcing the sample downstream within the microfluidic network. Once the amplified sample is transferred into the detection chambers 372 a-f, the amplified sample is isolated within the detection chambers 372 a-f of the microfluidic network. In some embodiments, isolating the amplified sample within the detection chambers 372 a-f can comprise closing detection valves 370 a, 370 b located upstream and downstream of the detection chambers 372 a-f. In some embodiments, the detection valves 370 a, 370 b located upstream and downstream of the detection chamber(s) comprise a TRS, and are closed by heating the TRS to seal the upstream and downstream channels, respectively, that are in communication with the detection chambers 370 a, 370 b.

Once isolated inside the detection chambers 372 a-f, the amplified sample can be contacted with, or mixed with a fluorescent moiety that is specific for the target nucleic acid and target amplicon, to create a detection mixture. In some embodiments, the fluorescent moiety can comprise an oligonucleotide probe operably coupled to a fluorescent moiety that is complementary to, or substantially complementary to, a nucleotide sequence within the target amplicon. In some embodiments, the term “specific for,” in reference to oligonucleotides and probes, refers to an oligonucleotide or probe that hybridizes exclusively or only to a cognate target sequence, under standard PCR/annealing conditions as described elsewhere herein.

In some embodiments, the microfluidic cartridges 200 can include oligonucleotide probes, e.g., in a lyophilized form, in the detection chambers 372 a-f. In some embodiments, oligonucleotide probes can be added to the microfluidic network after the sample to be analyzed has been introduced into the microfluidic cartridge. In some embodiments, probes in the form of lyophilized beads can be placed in the detection chambers 372 a-f of the cartridge 200 during the cartridge manufacturing process. In this embodiment, the lyophilized beads are larger in diameter than the diameters of the subchannels 365 a 1-365 a 3 and 365 b 1-365 b 3 leading into the detection chambers 372 a-f and subchannels 367 a, 367 b leading out of the detection chambers 372 a-f. In this manner, the lyophilized beads are blocked from leaving the detection chambers 372 a-f after final manufacture of the cartridge 200 and remain in the detection chambers 372 a-f during transportation and use.

In some embodiments, the probes are inserted into the detection chambers 372 a-f during the manufacture of the cartridge 200 using a drying process. In this embodiment, an amount of probe in liquid solution is added to each of the detection chamber 372 a-f; then the liquid is dried, evaporating the solvent and leaving the dried-on probe in each of the detection chambers 372 a-f. Whether the probe used is a lyophilized bead or is dried-on, an excess amount of the probe can be placed in the detection chambers 372 a-f to compensate for a portion that may dissolve in the sample 350 that passes through the detection chambers 372 a-f and enters the subchannels 367 a, 367 b and the fourth channel 374.

The skilled artisan will appreciate that several probe technologies are useful in the embodiments described herein. By way of example, the embodiments disclosed herein can be used with TAQMAN™ probes, molecular beacon probes, SCORPION™ probes, Sunrise probes, and the like.

TaqMan™ assays are homogenous assays for detecting polynucleotides (see U.S. Pat. No. 5,723,591). In TAQMAN™ assays, two amplification primers flank a central TAQMAN™ probe oligonucleotide. The probe oligonucleotide contains a fluorophore and quencher. During the polymerization step of the amplification process, the 5′ nuclease activity of the polymerase cleaves the probe oligonucleotide, causing the fluorophore moiety to become physically separated from the quencher, which increases fluorescence emission. As more amplicon is created, the intensity of emission at the novel wavelength increases.

Molecular beacons are an alternative to TAQMAN™ probes for the detection of polynucleotides (see U.S. Pat. Nos. 6,277,607; 6,150,097; and 6,037,130). Molecular beacons are oligonucleotide hairpins which undergo a conformational change upon binding to a perfectly matched template. The conformational change of the oligonucleotide increases the physical distance between a fluorophore moiety and a quencher moiety present on the oligonucleotide. This increase in physical distance causes the effect of the quencher to be diminished, thereby increasing the signal derived from the fluorophore.

Another method of detection useful in the embodiments disclosed herein includes the “adjacent probes method.” In this method, PCR is used to amplify the target sequence in the presence of two nucleic acid probes that hybridize to adjacent regions of the target sequence. One of the probes is labeled with an acceptor fluorophore and the other probe labeled with a donor fluorophore of a fluorescence energy transfer pair. Upon hybridization of the two probes with the target sequence, the donor fluorophore interacts with the acceptor fluorophore to generate a detectable signal. The sample is then excited with light at a wavelength absorbed by the donor fluorophore and the fluorescent emission from the fluorescence energy transfer pair is detected for the determination of that target amount. The “adjacent probes method” is disclosed, e.g., in U.S. Pat. No. 6,174,670B1.

Another method useful in the embodiments disclosed herein include the use of “sunrise primers.” Sunrise primers utilize a hairpin structure similar to molecular beacons, but in contrast to molecular beacons, are attached to a target binding sequence which serves as a primer. When the primer's complementary strand is synthesized, the hairpin structure is disrupted, thereby eliminating quenching. These primers detect amplified product and do not require the use of a polymerase with a 5′ exonuclease activity. Sunrise primers are described by Nazarenko et al. (Nucleic Acids Res. 25:2516-21 (1997) and in U.S. Pat. No. 5,866,336).

Yet another method useful in the embodiments disclosed herein include the use of SCORPION™ probes. SCORPION™ probes combine a primer with an added hairpin structure, similar to Sunrise primers. However, the hairpin structure of SCORPION™ probes is not opened by synthesis of the complementary strand, but by hybridization of part of the hairpin structure with a portion of the target which is downstream from the portion which hybridizes to the primer.

DzyNA-PCR is another method useful in the embodiments disclosed herein, that involves the use of a primer containing the antisense sequence of a DNAzyme, which is an oligonucleotide capable of cleaving specific RNA phosphodiester bonds. The primer binds to a target sequence and drives an amplification reaction producing an amplicon which contains the active DNAzyme. The active DNAzyme then cleaves a generic reporter substrate in the reaction mixture. The reporter substrate contains a fluorophore-quencher pair, and cleavage of the substrate produces a fluorescence signal which increases with the amplification of the target sequence. DzyNA-PCR is described in Todd et al., Clin. Chem. 46:625-30 (2000), and in U.S. Pat. No. 6,140,055.

Still other embodiments disclosed herein include the use of a “Q-PNA probe,” that is a quenchere-labeled peptide nucleic acid, in conjunction with a fluorophore-labeled oligonucleotide primer. The Q-PNA hybridizes to a tag sequence at the 5′ end of the primer. The use of Q-PNA probes is described in Fiandaca et al. Genome Research. 11:609-613 (2001).

Li et al. describes a double stranded probe having a quencher and fluorophore on opposite oligonucleotide strands. Li et al. Nucleic Acids Research. 30: 1-9. When not bound to the target, the strands hybridize to each other and the probe is quenched. However, when a target is present at least one strand hybridizes to the target resulting in a fluorescent signal.

Fluorescent Moieties

As discussed above, some embodiments, disclosed herein include contacting the an amplified sample with a fluorescent moiety, e.g., a fluourescent moiety that is operably coupled to an oligonucleotide that is specific for a polynucleotide sequence found within the target amplicon. Several fluorescent moieties useful in the embodiments disclosed herein are known in the art. By way of example, fluorophore labels and moieties useful in the embodiments and probes disclosed herein include, but are not limited to, dyes of the fluorescein family, the carboxyrhodamine family, the cyanine family, and the rhodamine family. Other families of dyes that can be used in the invention include, e.g., polyhalofluorescein-family dyes, hexachlorofluorescein-family dyes, coumarin-family dyes, oxazine-family dyes, thiazine-family dyes, squaraine-family dyes, chelated lanthanide-family dyes, the family of dyes available under the trade designation Alexa Fluor J, from Molecular Probes, and the family of dyes available under the trade designation Bodipy J, from Invitrogen (Carlsbad, Calif.). Dyes of the fluorescein family include, e.g., 6-carboxyfluorescein (FAM), 2′,4′,1,4,-tetrachlorofluorescein (TET), 2′,4′,5′,7′,1,4-hexachlorofluorescein (HEX), 2′,7′-dimethoxy-4′,5′-dichloro-6-carboxyrhodamine (JOE), 2′-chloro-5′-fluoro-7′,8′-fused phenyl-1,4-dichloro-6-carboxyfluorescein (NED), 2′-chloro-7′-phenyl-1,4-dichloro-6-carboxyfluorescein (VIC), 6-carboxy-X-rhodamine (ROX), and 2′,4′,5′,7′-tetrachloro-5-carboxy-fluorescein (ZOE). Dyes of the carboxyrhodamine family include tetramethyl-6-carboxyrhodamine (TAMRA), tetrapropano-6-carboxyrhodamine (ROX), Texas Red, R110, and R6G. Dyes of the cyanine family include Cy2, Cy3, Cy3.5, Cy5, Cy5.5, and Cy7. Fluorophores are readily available commercially from, for instance, Perkin-Elmer (Foster City, Calif.), Molecular Probes, Inc. (Eugene, Oreg.), and Amersham GE Healthcare (Piscataway, N.J.).

As discussed above, in some embodiments, probes used in the methods disclosed herein can comprise a quencher. Quenchers may be fluorescent quenchers or non-fluorescent quenchers. Fluorescent quenchers include, but are not limited to, TAMRA, ROX, DABCYL, DABSYL, cyanine dyes including nitrothiazole blue (NTB), anthraquinone, malachite green, nitrothiazole, and nitroimidazole compounds. Exemplary non-fluorescent quenchers that dissipate energy absorbed from a fluorophore include those available under the trade designation Black Hole™ from Biosearch Technologies, Inc. (Novato, Calif.), those available under the trade designation Eclipse™. Dark, from Epoch Biosciences (Bothell, Wash.), those available under the trade designation Qx1J, from Anaspec, Inc. (San Jose, Calif.), and those available under the trade designation Iowa Black™ from Integrated DNA Technologies (Coralville, Iowa).

Typically, a fluorophore and a quencher are used together, and may be on the same or different oligonucleotides. When paired together, a fluorophore and fluorescent quencher can be referred to as a donor fluorophore and acceptor fluorophore, respectively. A number of convenient fluorophore/quencher pairs are known in the art (see, for example, Glazer et al, Current Opinion in Biotechnology, 1997; 8:94-102; Tyagi et al., 1998, Nat. Biotechnol., 16:49-53) and are readily available commercially from, for instance, Molecular Probes (Junction City, Oreg.), and Applied Biosystems (Foster City, Calif.). Examples of donor fluorophores that can be used with various acceptor fluorophores include, but are not limited to, fluorescein, Lucifer Yellow, B-phycoerythrin, 9-acridineisothiocyanate, Lucifer Yellow VS, 4-acetamido-4′-isothio-cyanatostilbene-2,2′-disulfonic acid, 7-diethylamino-3-(4′-isothiocyanatophenyl)-4-methylcoumarin, succinimdyl 1-pyrenebutyrate, and 4-acetamido-4′-isothiocyanatostilbene-2-,2′-disulfonic acid derivatives. Acceptor fluorophores typically depend upon the donor fluorophore used. Examples of acceptor fluorophores include, but are not limited to, LC-Red 640, LC-Red 705, Cy5, Cy5.5, Lissamine rhodamine B sulfonyl chloride, tetramethyl rhodamine isothiocyanate, rhodamine x isothiocyanate, erythrosine isothiocyanate, fluorescein, diethylenetriamine pentaacetate or other chelates of Lanthanide ions (e.g., Europium, or Terbium). Donor and acceptor fluorophores are readily available commercially from, for instance, Molecular Probes or Sigma Chemical Co. (St. Louis, Mo.).

In some embodiments, after the amplification reaction has been mixed with the probe(s), the detection reaction is subjected to a detection thermocycling reaction. The detection thermocycling can involve heating the detection reaction so as to denature the double-stranded polynucleotides, followed by continuously ramping the temperature up or down over a set period of time and analyzing melting and reannealing curves. The use of fluorescence melting curves to monitor hybridization has been described, e.g, in L. E. Morrison & L. M. Stols, Sensitive fluorescence-based thermodynamic and kinetic measurements of DNA hybridization in solution, 32 Biochemistry 3095-3104, 1993), U.S. Pat. No. 6,174,670, and in U.S. Pat. No. 6,140,054 the entire contents of which are each herein incorporated by reference.

In some embodiments, the detection comprises illuminating the detection reaction with a wavelength of light for eliciting fluorescence by the fluorescent moiety, and continuously monitoring, as a function of temperature, the fluorescence emitted. In some embodiments, more than one fluorescent moiety, e.g., 2, 3, 4, 5, 6, or more, wherein each fluorescent moiety is specific for a different nucleic acid sequence present in a target amplicon, can be mixed with the amplified sample in the detection chambers 372 a-f. The use of more than one fluorescent moiety, wherein each fluorescent moiety is specific for a different nucleic acid sequence, enables the specific hybridization to (and thus detection of) more than one target nucleic acid sequence sequence, whether the different target nucleic acid sequences are present within a single amplicon, or whether the different target nucleic acid sequences are located within different amplicons, e.g., different amplicons generated by a multiplex PCR reaction in the amplification stage of the reaction.

In some embodiments, different oligonucleotide probes that are substantially complementary to different target nucleic acid sequences (within a single amplicon, or in different amplicons), and that are each operably coupled to a single fluorescent moiety can be used to detect multiple target sequences (e.g., different loci within a single amplicon or different amplicons) in a single detection reaction. For example, different oligonucleotides, preferably that have distinct T_(m)'s can each be operably coupled to a single type of fluorescent moiety. Because each different oligonucleotide probe has a distinct T_(m), the presence of the target nucleotide sequence within an amplicon(s) can be monitored by measuring the fluorescence emission as a function of temperature at a single emission wavelength. By way of example, in some embodiments, each detection chamber 372 a-f can contain oligonucleotide probes that comprise two, three, four, or more different nucleic acid sequences, each having distinct T_(m)'s, and each oligonucleotide being operably coupled to the same type of fluorescent moiety.

Alternatively, a single detection reaction can include a number of oligonucleotide different probes, each of which has a different oligonucleotide sequence, wherein each different oligonucleotide sequence is be operably coupled to different type of fluorescent moiety. This way, the each different probe within the detection reaction can be distinguished from other probes based on the distinguishable emission spectra of the fluorescent moieties. Preferably, the emission spectra of the different fluorescent moieties do not overlap, or do not have significant overlap, such that the different fluorescent moieties can be readily distinguished.

In some embodiments, the protocol used in the detection chambers 372 a-f can include subjecting the detection reaction to an initial cycle to melt double stranded nucleic acids including any target amplicons, and lowering the temperature to allow the annealing of one or more oligonucleotide probes to anneal to complementary (or substantially complementary) sequences of the single stranded amplicon DNA, to form a duplex. By way of example, in some embodiments, the detection reaction can be heated in order to ensure complete denaturation of double stranded nucleic acids in the detection mixture, including denaturation of target amplicon sequences. By way of example only, the detection reaction can be heated to about 90-100° C. for a period of time, e.g., about 15 sec to about 1 min. Following denaturation, the temperature of the detection mixture is lowered to allow annealing of probe(s) to target sequence(s). By way of example only, the annealing step can include cooling the detection reaction to about 45° C. for a period of time, e.g., for about 15 seconds to a minute, or longer, or any period of time in between, e.g., 30 sec.

After the annealing step, the temperature of the detection mixture can be slowly raised within the detection chamber 372 a-f, while continuously observing a fluorescence signal, in order to monitor (and record) the dissociation of, or melting of, the duplex formed by the probe and amplicon sequence. Specifically, the temperature of the detection mixture can incrementally ramped from the annealing temperature to a second temperature (e.g., the denaturation temperature). For example, in some embodiments, the detection reaction is ramped from the annealing temperature (or a first temperature that is lower than the T_(m) of any probe in the detection mixture), to the second temperature in increments of 0.05° C., 0.1° C., 0.2° C., 0.3° C., 0.4° C., 0.5° C., 0.6° C., 1.0° C., 1.5° C., 2.0° C., 2.5° C., 3.0° C., 3.5° C., 4.0° C., 4.5° C., 5.0° C., or greater, or any increment in between. Using the devices disclosed herein, the fluorescence signal emitted at each temperature increment is measured using the heater/detector module disclosed herein. In some embodiments, the ramping from annealing temperature to the second temperature (e.g., melting temperature), is referred to as a “melt protocol.” The change in fluorescence caused by the dissociation of a fluorescent probe from a cognate target sequence throughout the course of the melt protocol can be monitored over time/temperature during the melt protocol, and can be used to determine the presence and/or amount of a target sequence.

In some embodiments, the heating of the detection chambers 372 a-f can be synchronized and staggered in order to achieve a desired detector cycle time. For example, in some embodiments, the total time for melt protocol/detection is less than 30 minutes, e.g., between about 8-27 minutes, 10-26 minutes, 15-25 minutes, 20-25 minutes, or the like. By way of example, in some embodiments, the melt protocol takes about 22-25 minutes. In some embodiments, each of the detection chambers 372 a-f within a sample lane 300 is subjected to the same melt protocol. In some embodiments, some of the detection chambers 372 a-f within a sample lane 300 are subjected to different melt protocols.

In some embodiments, more than one probe with a single species of fluorescent moiety can be used in the same detection chamber, wherein each probe comprises a different oligonucleotide sequence, and wherein each probe has a different T_(m). For example, in some embodiments, two, three, four, or more, different probes with the same species of fluorescent moiety can be used in the same detection chamber, in order to detect two, three, four, or more, different target nucleic acid sequences.

Accordingly, in some embodiments, each lane 300 can be used to detect numerous target nucleic acid sequences. By way of example only, in some embodiments, 108 different target nucleic acid sequences can be detected in each of the lanes. Specifically, each detection chamber 372 a-f can include multiple different probes, e.g., eighteen different probes, wherein the probes comprise eighteen different oligonucleotide sequences specific for eighteen different target nucleic acid sequences, and wherein the probes collectively comprise six different types of fluorescent moieties (i.e., three different oligonucleotide sequences having distinct T_(m)'s can be coupled to a single type of fluorescent moiety). In this way, six different fluorescent moieties times three different oligonucleotide probes/each moiety times six different detection chambers, can be used to detect 108 different target nucleic acids.

FIGS. 10A-D provide representations of the microfluidic network of the sample lane 300, such as the sample lanes 300 located in the cartridge 200. FIGS. 10A-D illustrate the movement of a sample 350 as the sample 350 is processed in the microfluidic network, as it undergoes thermocycling and detection in the amplification chamber 362 and detection chambers 372 a-f.

Before introducing the sample 350 into the sample lane 300, the cartridge 200 can be positioned to receive the sample 350 from the fluid dispenser 400. Referring to FIG. 1C, the receiving tray 520 a may be opened, with the cartridge 200 positioned in the recessed bay 524 of the receiving tray 520 a. The fluid dispenser 400 can withdraw the prepared sample 350 from the process tube 32 in the rack 24 into a pipette 402 of the fluid dispenser 400 and carry the sample 350 in the pipette 402 to a position approximate to the cartridge 200 in the receiving tray 520. The fluid dispenser 400 can position the pipette tip 402 in the inlet 302. The fluid dispenser 400 can then dispense a volume of the sample 350 from the pipette tip 402 into the sample lane 300 through the inlet 302 of the sample lane 300. The volume of the sample 350 introduced into the inlet 302 can be, for example, approximately 10 μl. FIG. 10A illustrates the state of sample processing within the microfluidic network following introduction of the sample 350 into the sample lane 300 through the inlet 302 of the sample lane 300.

In some embodiments, prior to introduction of the sample 350 into the sample lane 300, the first and second amplification gates 310 a, b of the sample lane 300 can be in a closed state, such that the TRS (e.g., wax) 345 is positioned in the first channel 360 to obstruct passage of the sample 350 through the gates 310 a, 310 b. In some embodiment, prior to introduction of the sample 350 into the sample lane 300, the first and second amplification valves 330 a, 330 b of the sample lane 300 can be in an open state, such that the TRS 345 is maintained in the wax loading channel 334, and therefore is not blocking passage of the sample 350 in the first channel 360 near the valves 330 a, b. Thus, when the sample 350 is introduced into the microfluidic network, the sample 350 can bypass the closed amplification gate 310 a (including the upstream 318 and downstream 320 sides of the amplification gate 310 a) by following the route of the first channel 360 past the open first amplification valve 330 a in the first channel 360. In this manner, the sample 350 can travel from the inlet 302, through the first channel 360, into the amplification chamber 362, thereby filling the amplification chamber 362 to capacity. In some embodiments the amplification chamber has a volumetric capacity of 8 μl. The volume of the sample 350 initially introduced into the sample 350 may be of a volume in excess of the volume of the amplification chamber 362. Any volume of the sample 350 in excess of the volume of the amplification chamber 362 can exit the amplification chamber 362 at a downstream side of the amplification chamber 362 and may enter the second channel 364.

The second channel 364 can extend from the amplification chamber 362 past the second amplification gate 310 b into the second stage 208 of the microfluidic network of the sample lane 300. Because the second amplification gate 310 b may be initially closed when the sample 350 is introduced into the sample lane 300, the sample 350 can be blocked by the second amplification gate 310 b in the second channel 364 and diverted into the third channel 366. In the third channel 366, the sample can move past the second amplification valve 330 b to the first vent 368. Any volume of the sample 350 in the third channel in excess of the volume of the third channel 366 can be drained and removed from the microfluidic network through the first vent 368.

In some embodiments, upon introduction of the sample 350 into the microfluidic network, the pipette tip 402 of the liquid dispenser 400 can be removed from the inlet 302 and the receiving tray 520 can be closed, thereby sliding the receiving tray 520 under the optical module 502. The force member (not shown) can then elevate the receiving tray 520 upward toward the bottom side 506 of the optical module 502 in order to press the cartridge 200 against the aperture plate 540 of the optical module 502. Pressing the cartridge 200 upward against the aperture plate 540 can cause the cartridge 200 to experience a physical pressure against the aperture plate 540. The physical pressure applied to the cartridge 200 by the aperture plate 540 can also cause the cartridge 200 to likewise apply a downward pressure against the heater substrate 600 in the receiving tray 520. The pressure applied to the cartridge 200 on its top side by the aperture plate 540 and on its bottom side by the heater substrate 600 can be applied in a substantially uniform manner throughout the cartridge 200 such that all portion of the cartridge 200 in the recessed bay 524 of the receiving tray 520 can experiencing the same degree of pressure.

With the cartridge 200 positioned in the recessed bay 524 of the receiving tray 520, the various heaters of the heater substrate 600 can be in physical and/or thermal contact with the corresponding components (e.g., valves and gates) of the sample lanes 300 in cartridge 200. After the sample 350 is introduced into the sample lane 300 through the inlet 302 and the sample 350 is positioned in the first stage 206 of the sample lane 300, as shown in FIG. 10A, and physical pressure is applied between the cartridge 200 and the heater substrate 600, the first and second amplification valve heaters 630 a, 630 b can be turned on by sending the necessary electronic signals to the heaters. As illustrated in FIG. 10B, activating the first and second amplification valve heaters 630 a, 630 b, while bringing the activated heaters into physical and/or thermal contact with the first and second amplification valves 330 a, 330 b, can cause the TRS (e.g., wax) 345 in the first and second amplification valves 330 a, 330 b to melt and become mobile. As described in relation to FIGS. 4A-C, the mobile TRS 345 can then be expelled from the loading channel 334 by, for example, the expansion of the heated air in the valve loading port 332 of each of the first and second amplification valves 330 a, b. The TRS 345 may then enter the first and second channels 360 and 364 at the valve junctions 336 of the respective valves 330 a, b. The first and second amplification valve heaters 630 a, b can then be turned off and the TRS 345 may cool, solidify, and become immobile in the valve junctions 336, thereby closing the first and second amplification valves 330 a, 330 b and sealing the first and second channels 360, 364 to prevent further movement of the sample 350 in either the upstream or downstream direction in the first stage 206 of the sample lane 300. Thus, at this stage of the sample processing, the first and second amplification valves 330 a, b and the first and second amplification gates 310 a, b are in a closed position, thereby isolating the sample 350 in the first stage 206 of the sample lane 300. A majority portion of the isolated sample 350 is contained in the amplification chamber 362. Thus, the sample 345 is isolated in the first stage 206 of the microfluidic network, being specifically isolated in the amplification chamber 362 in order to undergo thermocycling to amplify target polynucleotides present in the sample 350 by, for example, PCR.

After completion of the amplification protocol in the amplification chamber 362, the amplified sample 350 can then be moved to the second stage 208 of the microfluidic network in the sample lane 300. Movement of the sample 350 from the first stage 206 into the detection chambers 372 a-f of the second stage 208 is illustrated in FIG. 10C. To effectuate the movement of the sample 350 out of the first stage 206 and into the second stage 208, the initially-closed second amplification gate 310 b can be opened and a motive force can be applied to the sample 350 to propel the sample 350 through the second channel 364 to the detection chambers 372 a-f.

Prior to, and as a part of, advancing the sample 350 from the first stage 206 of the sample lane 300 to the second stage 208 of the sample lane 300, the receiving tray 520 can be opened in order to allow the fluid dispenser 400 to act on the cartridge 200. For each sample lane 300 being processed simultaneously in the cartridge 200, a pipette tip 402 of the fluid dispenser 400 can again be positioned in the inlet 302 of the sample lane 300. The actions of the fluid dispenser 400 on the cartridge 200 can be two-fold. The fluid dispenser 400 can be used to supply both physical pressure and air pressure to the cartridge 200.

When the receiving tray 520 is open and the cartridge 200 is no longer in a position under the aperture plate 540, the cartridge 200 is no longer receiving pressure from the aperture plate 540 to press it against the heater substrate 600. When receiving tray 520 is open and when the pipette tip 402 is inserted into the inlet 302 of a sample lane 300, the fluid dispenser can be activated to press the pipette tip 402 into the inlet 302 with additional pressure in order to press the cartridge 200 against the heater substrate 600. Thus, at this stage of the sample processing, the physical pressure between the cartridge 200 and the heater substrate 600 is provided by the physical pressure of the fluid dispenser 400 in pressing the pipette into the inlet 302.

When a pipette 402 is inserted into the inlet 302, the fluid dispenser 400 can introduce air or another gas into the microfluidic network of the sample lane 300 through the inlet 302, thus supplying an air pressure to the microfluidic network. As represented in FIG. 10C, the air pressure supplied to the microfluidic network can push on the portion of the sample 350 located in the first channel 360, which is isolated upstream of the first amplification gate 310 a and first amplification valve 330 a, both of which are in a closed position at this stage of the sample processing. Concurrent with dispensing the air or gas into the microfluidic network, the fluid dispenser 400 can be lowered to force the pipette tips 402 against the inlet 302 to supply the additional physical pressure on the cartridge 302, thereby keeping the first and second amplification gates 310 a, b in physical contact with the respective amplification gate heaters 610 a, b. The first and second amplification gate heaters 610 a, b can then be activated in order to supply heat to the first and second amplification gates 310 a, 310 b. The heat from the amplification gate heaters 610 a, 610 b can melt the TRS 345 at the gate junctions 316 of the first and second amplification gates 310 a, 310 b in the first and second channels 360, 364, thus causing the TRS 345 to become mobile. The air pressure supplied to the sample 350 in the first channel 360 by the fluid dispenser 360 provides a force to the now-mobile TRS 345 at gate junction 316 of the first amplification gate 310 a. The air pressure from the fluid dispenser 400 is sufficient to dislodge the mobile TRS 345 in the first amplification gate 310 a in order to begin to move the TRS 345 downstream through the first channel 360. When the TRS 345 in the first amplification gate 310 a is dislodged, the pressure against the sample 350 is then propagated downstream to the melted and mobile TRS 345 in the junction 316 of the second amplification gate 310 b, thus also dislodging the TRS 345 in the second amplification gate 310 b. With the TRS 345 removed from the junctions 316 of the first and second amplification gates 310 a, b, the air pressure supplied by the fluid dispenser 400 is able to propel the majority of the sample 350 downstream into the second stage 208 of the sample lane 300. The TRS 345 dislodged from the first and second amplification gates 310 a, 310 b can move downstream along with the sample 350 as the sample 350 comes to occupy the detection chambers 372 a-f. Any sample 350 volume in excess of the volume of the detection chambers 372 a-f can continue travel beyond the detection chambers 372 a-f into the subchannels 367 a, 367 b downstream of the detection chambers 372 a-f. Additional excess sample 350 volume beyond the capacity of the detection chambers 372 a-f can also travel downstream of the detection chambers 372 a-f, through the subchannels 367 a, 367 b and past the second detection valve 370 b, into the fourth channel 374. Additional excess sample 350 can be drained from the microfluidic network through the second vent 376 downstream of, and in fluid communication with, the fourth channel 374. Any TRS 345 in the detection chambers 372 a-f downstream of the first and second amplification gates 310 a, 310 b does not interfere with any thermocycling or detection processes conducted in the detection chambers 372 a-f.

As the sample 350 is moved into the detection chambers 372 a-f as described above, the sample 350 comes into contact with the probes that were initially placed in the detection chambers 372 a-f prior to use or during manufacture of the cartridge 200. Upon entry of the sample into the detection chambers 372 a-f, the probes are dissolved into the sample 350 solution and bind to the polynucleotides in the sample 350 as described herein. Because an excess portion of the sample 350 will pass through the detection chambers 372 a-f into the subchannels 367 a, 367 b and fourth channel 374, an excess amount of the probe can also initially be placed into the detection chambers 372 a-f to compensate for the portion that may lost as it is absorbed by and passes downstream with the excess portion of the sample 350.

It is noted that the first and second amplification valves 330 a, 330 b can remain closed when the first and second amplification gates 310 a, 310 b are opened. This is possible because when the first and second amplification gate heaters 610 a, 610 b are activated to heat up the TRS 645 in the gate junctions 316, the first and second amplification valve heaters 630 a, 630 b are not activated, thus leaving the TRS in the valve junctions 336 in a solidified state. Furthermore, the closed first and second amplification valves 330 a, b are sufficiently stable to not open again when the air pressure is applied by the fluid dispenser 400, in part because the valve junctions 336 are wider than the gate junctions 316 and thus can hold a greater quantity of TRS 345, the greater quantity of TRS 345 being more difficult to dislodge from the valve junction 336. Thus, closing the initially-open first and second amplification valves 330 a, 330 b is the mechanism by which the sample 350 becomes isolated in the amplification chamber 362. Conversely, opening the initially-closed first and second amplification gates 310 a, 310 b (along with supplying the air pressure) is the mechanism by which the sample 350 is moved from the first stage 206 of the sample lane 300 to the second stage 208 of the sample lane 300.

FIG. 10C shows that the sample 350 is located primarily in the second stage 208 of the sample lane 300 after the sample 350 has been displaced from the first stage 206 of the sample lane 300. At this point in the sample processing, the pipette tips 402 of the liquid dispenser 400 can be removed from the inlet 302 and the receiving tray 520 can once again be closed, thereby sliding the receiving tray 520 under the optical module 502 of the heater/optical unit 500. The force member is again used to apply upward pressure on the receiving tray 520, wherein the heater substrate 600 applies pressure against the cartridge 200 and the cartridge 200 likewise applies pressure against the aperture plate 540. When physical pressure is applied between the cartridge 200 and the heater substrate 600 and the aperture plate 540, the first and second detection valve heaters 670 a, b can also be activated by sending the necessary electronic signals to the heaters.

As illustrated in FIG. 10D, activating the first and second detection valve heaters 670 a, 670 b while bringing the heaters in physical and/or thermal contact with the first and second detection valves 370 a, b, can cause the TRS (e.g., wax) 345 in the first and second detection valves 370 a, b to melt and become mobile. The mobile TRS 345 can then be expelled from the loading channel 334 by, for example, the expansion of the heated air in the valve loading port 332 of each of the first and second detection valves 370 a, b. The TRS 345 may then enter the second and fourth channels 364, 374 at the valve junctions 336 of the respective valves 370 a, b. The first and second detection valve heaters 670 a, 670 b are then turned off and the TRS 345 may cool, solidify, and become immobile in the valve junctions 336, thereby closing the first and second detection valves 370 a, 370 b and sealing the second and fourth channels 364, 374 to prevent further movement of the sample 350 in either the upstream or downstream direction in the second stage 208 of the sample lane 300. Thus, the first and second detection valves 370 a, 370 b are now closed, isolating a majority portion of the sample 350 in the detection chambers 372 a-f of the second stage 208 of the sample lane 300. The sample 350 is isolated in the detection chambers 372 a-f in order to undergo a thermocycling procedure for analyte detection, as described elsewhere herein.

Following processing of the sample 350 in the amplification chamber 362 and deposition of the amplified samples in detection chambers 372 a-f of the sample lane 300, the detector head 700 in the optical module 502 can conduct a detection procedure on the sample 350 in the detection chambers 372 a-f to determine if specific analyte amplicons are present in the sample 350.

Referring again to FIG. 7B, the detector head 700 is housed in the optical unit 502 of the heater/optical module 500. As shown in FIG. 8 , the detector head 700 is able to project light from the light sources 726 a, 727 a through the apertures 557 of the aperture plate 540 into the cartridge 200 and detect any fluorescence emitted from the detection chambers 372 a-f in the cartridge 200 using the light detectors 726 b, 727 b.

FIGS. 11A-11D illustrate the movement of the detector head 700 in the optical unit 500 above the microfluidic cartridge 200 during the analyte detection procedure. In the embodiment shown in FIGS. 11A-11D, the detector head 700 is comprised of two rows and six columns of detector pairs, each column being comprised of two detector pairs. Labels 722 a-733 a represent the light sources of the detector pairs 722-733 in the detector head 700.

FIG. 11A shows the detector head 700 in a position above the cartridge 200, such that the detector head 700 has already advanced partially along the length (x-axis) of the cartridge 200. Previously to the positioning shown in FIG. 11A, following calibration of the detector head 700 using the normalizer plate 546, the detector head 700 may begin the detection procedure at a position such that a first column C1 of detector pairs 732, 733 is located over the first column of detection chambers 372 a, 372 d in the sample lane 300 a. With the column C1 positioned over detection chambers 372 a, 372 d of sample lane 300 a, the light sources 732 a and 733 a may emit light into the detection chambers 372 a, 372 d, respectively. The light detectors 732 b and 733 b will detect the light emitted from the detection chambers 372 a, 372 d to determine the presence or absence of one or more analyte polynucleotide amplicons in the sample 350. Following light emission and detection at the first column of detection chambers, detection chambers 372 a, 372 d, of sample lane 300 a, the detector head 700 may advance lengthwise (along the x-axis) over the cartridge 200. The detector head 700 may advance to place the column C1 of detector pairs 732, 733 over the second column of detection chambers, detection chambers 372 b, 372 e, of sample lane 300 a. The column C1 of detector pairs 732, 733 may then conduct analyte detection on the detection chambers 372 b, 372 e, and then advance to the third column of detection chambers, detection chambers 372 c, 372 f, of the sample lane 300 a. After conducting analyte detection on all the detection chambers of sample lane 300 a, the detector head 700 may be advanced to position the column C1 of detector pairs 732, 733 over the first column of detection chambers 372 a, 372 d in the sample lane 300 b. When the column C1 of detector pairs 732, 733 is positioned over a column of detection chambers in the sample lane 300 b, the column C2 of detector pairs 730, 731 can be positioned over the corresponding first column of detection chambers 372 a, 372 d in the sample lane 300 a. The detector head 700 can continue advance lengthwise (along the x-axis) across the cartridge 200, thereby positioning each column C1-C6 of detector pairs over each column of detection chambers in each of the sample lanes 300 a-3001 of the cartridge 200. The wavelength of light produced and detected by each detector pair 722-733 may be different, thereby allowing for detection of a plurality of different polynucleotide markers using different fluorophore probes associated with the different markers.

FIG. 11A shows the detector head 700 positioned over the cartridge 200 so that the column C1 of detector pairs is positioned over the first column of detection chambers 372 a, 372 d of sample lane 300 f. Likewise, each of the other columns C2-C6 is positioned over the first column of detection chambers 372 a, 372 d in each of the sample lanes 300 f-300 a, respectively. FIG. 11B shows the advancement of the detector head 700 across the cartridge 200 so that each of the columns C1-C6 of detector pairs is positioned over the second column of detection chambers 372 b, 372 e in each of the sample lanes 300 f-300 a, respectively. FIG. 11C shows the advancement of the detector head 700 across the cartridge 200 so that each of the columns C1-C6 of detector pairs is positioned over the third column of detection chambers 372 c, 372 f in each of the sample lanes 300 f-300 a, respectively.

FIG. 11D shows the continued advancement of the detector head 700 across the cartridge 200 so that each of the columns C1-C6 of detector pairs is again positioned over the first column of the detection chambers in the sample lanes. FIG. 11D shows the detector head 700 positioned over the cartridge 200 so that each of the columns C1-C6 of detector pairs is positioned over the first column of detection chambers 372 a, 372 d in each of the sample lanes 300 b-300 g, respectively. With the detector head 700 positioned as shown in FIG. 11D, the detector head 700 has completed the detection procedure in the six detection chambers 372 a-f of sample lane 300 a. At this point, each detection chamber 372 a-f of sample lane 300 a has been optically scanned by six detector pairs. More specifically, detection chambers 372 d-f in the top group of detection chambers in the sample lane 300 a has been optically scanned by detector pairs 733, 731, 729, 727, 725, and 723 of row R1 of the detector head 700; detection chambers 372 a-c in the bottom group of detection chambers in the sample lane 300 a has been optically scanned by detector pairs 732, 730, 728, 726, 724, and 722 of row R2 of the detector head 700. The detector head 700 may continue to advance across the cartridge 200 until each of the detection chambers 372 a-f in each of the sample lanes 300 a-3001 has been optically scanned by the detector head 700.

Because of the arrangement of the detection chambers 372 a-f into rows and columns, each sample 350 in a sample lane 300 may undergo multiplexed amplicon detection. For example, each detection chamber 372 a-f can be optically scanned by six different detector pairs, the detection chambers 372 a-c being scanned by detector pairs in row R1 and the detection chambers 372 d-f being scanned by detector pairs in row R2 of the detector head 700. In certain embodiments, the detector pairs in each column can be configured to emit and detect light of the same wavelength (color) as each other, but wherein the wavelength is different than the light emitted and detected by the detector pairs in the other columns. Each column of detector pairs may emit and detect a unique wavelength of light, and as such the detector 700 may emit and detect light of six different wavelengths. Accordingly, each detection chamber 372 a-f in each of the sample lanes 300 a-l may be optically scanned by six different wavelengths of light. Alternatively, the detector pairs individually in each column C1-C6 may emit and detect a unique wavelength of light. Thus, the detector may emit and detect light of 12 different wavelengths, a different length emitted and detected by each detector pair 722-733.

Each of the detection chambers 372 a-f in each of the sample lanes 300 a-l may be pre-loaded with fluorescence probes, each of which can be associated with a certain wavelength (color); each probe also specifically binds to (e.g., under stringent conditions), a particular sequence to be detected (e.g., a target amplicon, a positive control sequence, or the like). When the sample 350 is moved into the detection chambers 372 a-f (as shown in FIG. 10C), one or more of the probes present in the detection chamber 372 a-f may bind with the analyte associated with the probe, if the analyte is indeed present in the sample 350. Each of the detection chambers 372 a-f may be pre-loaded with six different probes. Thus, the detection chambers 372 a-f of each sample lane 300 may contain a total of 36 different probes. Furthermore, each probe may undergo three melts in the detection chamber. Accordingly, each sample lane 300 can perform detection on up to 108 analytes.

The detection data obtained from the detector head 700 can be recorded and associated with the samples 350 in the sample lanes 300 a-l. Following completion of the detection procedure, the sample 350 may remain isolated in the detection chambers 372 a-f in the second stage 208 of the sample lanes 300 a-l. After the detection procedure is complete, the receiving tray 520 may be opened again and the cartridge 200 may be removed, in a manual or automated fashion, from the recessed bay 524 of the receiving tray 520. The cartridge 200 may be discarded.

The above description discloses several methods and systems of the embodiments disclosed herein. The embodiments disclosed herein are susceptible to modifications in the methods and materials, as well as alterations in the fabrication methods and equipment. Such modifications will become apparent to those skilled in the art from a consideration of this disclosure or practice of the invention disclosed herein. Consequently, it is not intended that the embodiments disclosed herein be limited to the specific embodiments disclosed herein, but that it cover all modifications and alternatives coming within the true scope and spirit of the invention.

All references cited herein including, but not limited to, published and unpublished applications, patents, and literature references, are incorporated herein by reference in their entirety and are hereby made a part of this specification. To the extent publications and patents or patent applications incorporated by reference contradict the disclosure contained in the specification, the specification is intended to supersede and/or take precedence over any such contradictory material. 

1-56. (canceled)
 57. A microfluidic cartridge comprising: a plurality of sample lanes, each lane comprising a microfluidic network having: an inlet; a single amplification chamber, wherein the single amplification chamber is configured to be heated in which polynucleotides are amplified within the single amplification chamber; a first amplification valve upstream of the single amplification chamber; a second amplification valve downstream of the single amplification chamber; a first channel configured for fluidically transmitting the polynucleotides from the inlet, via the first amplification valve, to the single amplification chamber; a plurality of detection chambers downstream of the single amplification chamber; a first detection valve downstream of the single amplification chamber and upstream of the plurality of detection chambers; a second detection valve downstream of the plurality of detection chambers, wherein the plurality of detection chambers are disposed between the first detection valve and the second detection valve; and a second channel configured for fluidically transmitting the amplified polynucleotides from the single amplification chamber to a plurality of subchannels, each subchannel connecting to one of the plurality of detection chambers, wherein the plurality of subchannels are configured to allow filling of the plurality of detection chambers with the amplified polynucleotides from the single amplification chamber.
 58. The microfluidic cartridge of claim 57, further comprising a third channel in each of the microfluidic networks, the third channel leading from the single amplification chamber to a first vent.
 59. The microfluidic cartridge of claim 57, further comprising a fourth channel in each of the microfluidic networks, the fourth channel leading from the plurality of detection chambers to a second vent.
 60. The microfluidic cartridge of claim 57, wherein the first amplification valve comprises a temperature responsive substance that melts upon heating to seal the first channel.
 61. The microfluidic cartridge of claim 57, wherein the second amplification valve comprises a temperature responsive substance that melts upon heating to seal the second channel.
 62. The microfluidic cartridge of claim 57, wherein the first detection valve comprises a temperature responsive substance that melts upon heating to seal the second channel.
 63. The microfluidic cartridge of claim 59, wherein the second detection valve comprises a temperature responsive substance that melts upon heating to seal the fourth channel.
 64. The microfluidic cartridge of claim 57, wherein the single amplification chamber has a volume of 5-10 μl.
 65. The microfluidic cartridge of claim 57, wherein one detection chamber of the plurality of detection chambers has a volume of approximately 1 μl.
 66. The microfluidic cartridge of claim 57, wherein each detection chamber of the plurality of detection chambers has a volume of approximately 1 μl.
 67. The microfluidic cartridge of claim 57, further comprising one or more fluorescence detection windows.
 68. A microfluidic cartridge comprising: a plurality of sample lanes, each lane comprised of a microfluidic network having a first stage and a second stage, wherein the first stage and the second stage are in fluid communication, the first stage comprising: an inlet; a single amplification chamber in fluid communication with the inlet, wherein the single amplification chamber is configured to be heated to amplify polynucleotides; a first amplification valve upstream of the single amplification chamber; a second amplification valve downstream of the single amplification chamber; the second stage downstream to the first stage comprising: a plurality of detection chambers; and a first detection valve upstream of the plurality of detection chambers; a second detection valve downstream of the plurality of detection chambers, the first detection valve and the second detection valve configured to isolate the amplified polynucleotides within the plurality of detection chambers, the amplified polynucleotides configured to be fluidically transmitted from the single amplification chamber of the first stage to the plurality of detection chambers of the second stage, wherein the plurality of detection chambers are disposed between the first detection valve and the second detection valve.
 69. The microfluidic cartridge of claim 68, wherein the first amplification valve and the second amplification valve comprise a temperature responsive substance that softens upon heating.
 70. The microfluidic cartridge of claim 68, wherein the first detection valve and the second detection valve comprise a temperature responsive substance that softens upon heating.
 71. The microfluidic cartridge of claim 68, wherein the first stage comprises a first vent.
 72. The microfluidic cartridge of claim 68, wherein the second stage comprises a second vent.
 73. The microfluidic cartridge of claim 68, wherein the second stage comprises one or more fluorescence detection windows.
 74. A microfluidic cartridge comprising: a plurality of sample lanes, each lane comprised of a microfluidic network comprising: one isolatable amplification chamber in which polynucleotides are amplified, wherein the one isolatable amplification chamber is configured to be heated to amplify polynucleotides; and a plurality of isolatable detection chambers downstream of the one isolatable amplification chamber, the plurality of detection chambers isolated by a first detection valve upstream of the plurality of detection chambers and a second detection valve downstream of the plurality of detection chambers, wherein the plurality of isolatable detection chambers are disposed between the first detection valve and the second detection valve, each detection chamber in fluid communication with the one isolatable amplification chamber such that each detection chamber receives a portion of the amplified polynucleotides from the one isolatable amplification chamber, wherein the one isolatable amplification chamber and the plurality of detection chambers are in fluid communication to allow filling of the plurality of detection chambers with amplified polynucleotides.
 75. The multiplexed microfluidic cartridge of claim 74, wherein each detection chamber has a volume of approximately 1 μl and wherein the one isolatable amplification chamber has a volume of approximately 5-10 μl.
 76. The microfluidic cartridge of claim 74, further comprising one or more fluorescence detection windows. 